WO2021176416A1 - Dispositif de champ lumineux, procédé de compensation d'aberration optique ou de rendu de simulation et système de test de la vision utilisant ceux-ci - Google Patents

Dispositif de champ lumineux, procédé de compensation d'aberration optique ou de rendu de simulation et système de test de la vision utilisant ceux-ci Download PDF

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Publication number
WO2021176416A1
WO2021176416A1 PCT/IB2021/051868 IB2021051868W WO2021176416A1 WO 2021176416 A1 WO2021176416 A1 WO 2021176416A1 IB 2021051868 W IB2021051868 W IB 2021051868W WO 2021176416 A1 WO2021176416 A1 WO 2021176416A1
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WO
WIPO (PCT)
Prior art keywords
location
phase element
computer
user
image
Prior art date
Application number
PCT/IB2021/051868
Other languages
English (en)
Inventor
Faleh Mohammad Faleh ALTAL
Guillaume Lussier
Matej Goc
Yaiza Garcia
Original Assignee
Evolution Optiks Limited
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US16/810,143 external-priority patent/US10761604B2/en
Priority claimed from US16/854,787 external-priority patent/US10860099B2/en
Priority claimed from PCT/IB2020/057887 external-priority patent/WO2021038421A1/fr
Priority claimed from PCT/US2020/058383 external-priority patent/WO2021087375A1/fr
Application filed by Evolution Optiks Limited filed Critical Evolution Optiks Limited
Priority to IL295827A priority Critical patent/IL295827A/en
Priority to EP21764574.6A priority patent/EP4115231A4/fr
Priority to CA3167642A priority patent/CA3167642A1/fr
Publication of WO2021176416A1 publication Critical patent/WO2021176416A1/fr
Priority to US17/510,297 priority patent/US11500460B2/en
Priority to US17/652,656 priority patent/US11500461B2/en
Priority to US17/819,885 priority patent/US11762463B2/en
Priority to US17/957,464 priority patent/US11789531B2/en
Priority to US18/343,642 priority patent/US20230341934A1/en

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Classifications

    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06F—ELECTRIC DIGITAL DATA PROCESSING
    • G06F3/00—Input arrangements for transferring data to be processed into a form capable of being handled by the computer; Output arrangements for transferring data from processing unit to output unit, e.g. interface arrangements
    • G06F3/01—Input arrangements or combined input and output arrangements for interaction between user and computer
    • G06F3/011—Arrangements for interaction with the human body, e.g. for user immersion in virtual reality
    • G06F3/013—Eye tracking input arrangements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/1015—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for wavefront analysis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/103—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining refraction, e.g. refractometers, skiascopes
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B3/00—Simple or compound lenses
    • G02B3/0006—Arrays
    • G02B3/0037—Arrays characterized by the distribution or form of lenses
    • G02B3/0056—Arrays characterized by the distribution or form of lenses arranged along two different directions in a plane, e.g. honeycomb arrangement of lenses
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06V—IMAGE OR VIDEO RECOGNITION OR UNDERSTANDING
    • G06V10/00—Arrangements for image or video recognition or understanding
    • G06V10/10—Image acquisition
    • G06V10/12—Details of acquisition arrangements; Constructional details thereof
    • G06V10/14—Optical characteristics of the device performing the acquisition or on the illumination arrangements
    • G06V10/147—Details of sensors, e.g. sensor lenses
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06V—IMAGE OR VIDEO RECOGNITION OR UNDERSTANDING
    • G06V40/00—Recognition of biometric, human-related or animal-related patterns in image or video data
    • G06V40/10—Human or animal bodies, e.g. vehicle occupants or pedestrians; Body parts, e.g. hands
    • G06V40/18—Eye characteristics, e.g. of the iris
    • G06V40/19—Sensors therefor

Definitions

  • the present disclosure relates to digital displays, and in particular, to a light field device, optical aberration compensation or simulation rendering method and vision testing system using same.
  • the operating systems of current electronic devices having graphical displays offer certain “Accessibility” features built into the software of the device to attempt to provide users with reduced vision the ability to read and view content on the electronic device.
  • current accessibility options include the ability to invert images, increase the image size, adjust brightness and contrast settings, bold text, view the device display only in grey, and for those with legal blindness, the use of speech technology.
  • Optical devices such as refractors and phoropters, are commonly used to test or evaluate the visual acuity of its users, for example, in the prescription of corrective eyewear, contact lenses or intraocular implants.
  • a computer- implemented method automatically implemented by one or more digital processors, to automatically adjust user perception of an input image to be rendered via a set of pixels and a corresponding array of light field shaping elements (LFSE), wherein the user perception is affected by an optical aberration
  • the method comprising: for each given pixel of at least some of the set of pixels: digitally projecting an adjusted image ray trace from said given pixel towards a user pupil location, given a corresponding LFSE corresponding thereto, to intersect a virtual phase element digitally defined between said given pixel and the user’s retina to virtually produce a designated optical phase shift corresponding to the optical aberration; digitally computing a corresponding refracted ray trace resulting from intersection of said adjusted image ray trace with said virtual phase element; digitally projecting said refracted ray trace to intersect an adjusted image plane location on a designated adjusted image plane; associating with said given pixel an adjusted image value designated for said adjusted image location; and rendering for each said given pixel said adjusted
  • the adjusted image plane comprises a pixel plane.
  • the optical aberration is defined by an eye focus parameter and a higher order aberration parameter, wherein said virtual phase element is defined as a function of said higher order aberration parameter, wherein said adjusted image plane comprises a virtual image plane virtually positioned relative to the digital display at a designated minimum viewing distance designated such that said perceptively adjusted version of the input image is adjusted to accommodate said eye focus parameter.
  • the aberration is defined by an eye focus parameter and a higher order aberration parameter, wherein said virtual phase element is defined as a function of said higher order aberration parameter, wherein said adjusted image plane is designated as a user retinal plane, and wherein said refracted ray trace is projected to intersect with said user retinal plane by further redirecting said refracted image ray trace given said pupil location in accordance with said eye focus parameter.
  • the virtual phase element is defined by a variable dioptric power, and wherein said refracted ray trace is refracted as a function of a given dioptric power defined for an intersection portion of said virtual phase element intersected by said adjusted image ray trace.
  • the variable dioptric power is profiled in accordance with a higher order aberration of the user’s eye.
  • variable dioptric power is profiled to simulate a progressive or bifocal lens.
  • the virtual phase element is defined by an input surface and an output surface, and wherein said refracted ray trace is digitally refracted to output said by sequentially computing a first refraction event at said input surface and a second refraction event at said output surface.
  • At least one of said input surface or said output surface has a variable profile.
  • the virtual phase element is defined by a height function characterizing said variable profile.
  • the height function is derived from a set of Zernike coefficients preset so as to reproduce said designated optical phase shift.
  • the virtual phase element is further defined by a normal vector function derived from said height function that characterizes an orientation of an output surface of said virtual phase element with respect to any location on an input surface of said virtual phase element.
  • the computing sequentially a first refraction event at said input surface and a second refraction event at said output surface comprises: identifying an input location of said adjusted ray trace on said input surface; computing a first refracted ray from said first refraction event at said input location; at least partially projecting said first refracted ray inside said virtual phase element; and computing said second refraction event using said normal vector function.
  • the at least partially proj ecting said first refracted ray inside said virtual phase element comprises: tracing said first refracted ray until it reaches a location on said output surface; wherein said normal vector function in said computing said second refraction event is the normal vector function at the input surface location corresponding to the location on said output surface.
  • the at least partially proj ecting said first refracted ray inside said phase element comprises: deriving a point on said output surface corresponding to said input location on said input surface but translated perpendicularly a value equal to said height function for that input location; wherein said normal vector function in said computing said second refraction event is the normal vector function at said input location.
  • the at least partially proj ecting said first refracted ray inside said phase element comprises: partially tracing said first refracted ray a length equal to said height function for that input location to a partial location; and translating said first refracted ray perpendicularly to said input surface towards said output surface until it reaches said second surface; wherein said normal vector function in said computing said second refraction event is said normal vector function at the input surface location corresponding to said partial location on said output surface.
  • the height function and said normal vector function are represented in memory in a data object comprising, respectively, a set of height values and associated normal vector values of said output surface corresponding to a plurality of surface locations on said input surface; wherein using said height function and said normal vector function involves fetching a height value and associated normal vector value corresponding to the surface location of said plurality of surface locations that is closest to said input location.
  • the data object is a texture data object.
  • the input image comprises distinct image portions, each image portion being associated with a distinct virtual phase element, and wherein said adjusted image ray trace for said distinct image portions intersects a corresponding one of said distinct virtual phase element to be processed accordingly.
  • the virtual phase element comprises a plurality of virtual phase elements, and wherein said adjusted image ray trace is sequentially processed to intersect sequential ones of said virtual phase elements in its path.
  • the optical aberration is defined by at least one of an astigmatism parameter, an eye focus parameter, or a higher order aberration parameter.
  • the virtual phase element is virtually located at a location between said given pixel and a user pupil location so as to at least partially simulate an intervening corrective lens defined to produce said designated phase shift in at least partially addressing the optical aberration.
  • the virtual phase element is virtually located so as to at least partially simulate an optical correction, at least partially defined by said designated phase shift when applied to compensate for the optical aberration, to be experienced by the user in selecting a corrective lens.
  • the virtual phase element is virtually located at a user’s eye pupil or lens location so to simulate an optical correction to be experienced by the user after undergoing a corresponding eye surgery or intraocular implant.
  • a computer-readable medium comprising instructions for implementation by one or more digital processors to automatically adjust user perception of an input image to be rendered via a set of pixels and a corresponding array of light field shaping elements (LFSE), wherein the user perception is affected by an optical aberration, by implementing a method a described above.
  • LFSE light field shaping elements
  • a device to automatically adjust user perception of an input image wherein the user perception is affected by an optical aberration
  • the device comprising: a digital display comprising a set of pixels; an array of light field shaping elements (LFSE) disposed relative to said set of pixels so to at least partially govern a light field emanated thereby; a digital processor; and a computer- readable medium as defined above.
  • LFSE light field shaping elements
  • a digital display device to automatically adjust user perception of an input image, wherein the user perception is affected by an optical aberration
  • the device comprising: a digital display comprising a set of pixels; an array of light field shaping elements (LFSE) disposed relative to said set of pixels so to at least partially govern a light field emanated thereby; and a digital processor operable to: receive as input an optical aberration parameter; digitally define a virtual phase element based at least in part on said optical aberration parameter to be virtually disposed between said pixels and the user’s retina to virtually produce a designated optical phase shift corresponding to the optical aberration; virtually trace a ray from each given pixel of at least some of said pixels to virtually interface with said virtual phase element so to define a corresponding refracted ray trace that intersects a respective adjusted image plane location; associate with said given pixel an adjusted image value designated for said respective adjusted image location; and render for each said given pixel said adjusted image value associated therewith.
  • LFSE light field shaping elements
  • the optical parameter comprises one or more polynomial coefficients.
  • the polynomial coefficients comprise Zernike coefficients.
  • the virtual phase element is defined by a data object comprising a set of height values and associated normal vector values corresponding with a plurality of virtual phase element surface locations.
  • the data object comprises texture data object.
  • the optical aberration parameter comprises an eye focus parameter and a higher order aberration parameter, wherein said virtual phase element is defined, at least in part, as a function of both said eye focus parameter and said higher order aberration parameter.
  • the optical aberration parameter comprises an eye focus parameter and a higher order aberration parameter, wherein said virtual phase element is defined, at least in part, as a function of said higher order aberration parameter, and wherein an adjusted image plane comprising each said adjusted image plane location is automatically designated as a function of said eye focus parameter so to distinctly compensate therefor.
  • the virtual phase element is virtually located at a location between said given pixel and a user pupil location so as to at least partially simulate an intervening corrective lens defined to produce said designated phase shift in at least partially addressing the optical aberration.
  • the virtual phase element is virtually located so as to at least partially simulate an optical correction, at least partially defined by said designated phase shift when applied to compensate for the optical aberration, to be experienced by the user in selecting a corrective lens.
  • the virtual phase element is virtually located at a user’s eye pupil or lens location so to simulate an optical correction to be experienced by the user after undergoing a corresponding eye surgery or intraocular implant.
  • a digital display device to automatically adjust user perception of an input image, wherein the user perception is affected by a higher order aberration
  • the device comprising: a digital display comprising a set of pixels; an array of light field shaping elements (LFSE) disposed relative to said set of pixels so to at least partially govern a light field emanated thereby; and a digital processor operable to: receive as input a set of higher order aberration parameters digitally defining the higher order aberration; for each given pixel of at least some of said pixels, identify an adjusted image plane location corresponding thereto given a corresponding LFSE corresponding thereto and given said set of higher order aberration parameters, and associate therewith an adjusted image value designated for said adjusted image location; and render for each said given pixel said adjusted image value associated therewith.
  • the set of higher order aberration parameters comprises a set of Zernike coefficients.
  • the user is further affected by a lower order aberration defined by an eye focus parameter, and wherein said adjusted image plane location is identified given said eye focus parameter and said set of higher order aberration parameters.
  • the user is further affected by a lower order aberration defined by an eye focus parameter, and wherein an adjusted image plane comprising each said adjusted image plane location is automatically designated as a function of said eye focus parameter so to distinctly compensate therefor.
  • the device simulates an intervening corrective lens that at least partially addresses the higher order aberration.
  • the device simulates a higher order optical correction to be experienced by the user in selecting a corrective lens.
  • the device simulates a higher order optical correction to be experience by the user after undergoing a corresponding eye surgery or intraocular implant.
  • FIGS. 1A and IB are schematic diagrams of an exemplary light field vision testing or previewing system, in accordance with one embodiment
  • Figures 2A to 2C schematically illustrate normal vision, blurred vision, and corrected vision in accordance with one embodiment, respectively;
  • Figures 3 A and 3B are schematic diagrams of a light field display in which respective pixel subsets are aligned to emit light through a corresponding microlens or lenslet, in accordance with one embodiment;
  • Figures 4A to 4C are schematic diagrams of exemplary light field vision testing or previewing systems (e.g. refractors/phoropters), in accordance with different embodiments;
  • Figure 5 is a plot of the angular resolution of an exemplary light field display as a function of the dioptric power generated, in accordance with one embodiment
  • Figures 6A to 6D are schematic plots of the image quality generated by a light field refractor/phoropter as a function of the dioptric power generated by using in combination with the light field display (A) no refractive component, (B) one refractive component, (C) and (D) a multiplicity of refractive components;
  • Figures 7A, 7B and 7C are perspective views of exemplary light field refractors/phoropters, showing a casing thereof in cross-section (A and B) and a unit combining side-by-side two of the units (C) shown in 7A and 7B, in accordance with one embodiment;
  • Figure 8 is a process flow diagram of an exemplary dynamic subjective vision testing method, in accordance with one embodiment
  • Figure 9 is a schematic diagram of an exemplary light field image showing two columns of optotypes at different dioptric power for the method of Figure 8, in accordance with one embodiment;
  • Figures 10A and 10B are process flow diagrams of exemplary input constant parameters and variables, respectively, for the ray -tracing rendering process of Figure 11, in accordance with one embodiment;
  • Figure 11 is a process flow diagram of an illustrative ray -tracing rendering process, in accordance with one embodiment
  • Figure 12 is a process flow diagram illustrating a process step of Figure 11, in accordance with one embodiment
  • Figure 13 is a process flow diagram illustrating certain process steps of Figure 11, in accordance with one embodiment.
  • Figures 14A and 14B are schematic diagrams illustrating certain process steps of Figure 11, in accordance with one embodiment;
  • Figure 15 is a schematic diagram illustrating the process steps of Figures 13 and 16, in accordance with one embodiment
  • Figure 16 is a process flow diagram illustrating certain process steps of Figure 11, in accordance with one embodiment
  • Figures 17A to 17D are schematic diagrams illustrating certain process steps of Figures 13 and 16, in accordance with one embodiment
  • Figures 18 and 19 are schematic diagrams illustrating ray -tracing in the context of non-parallel planes, in accordance with one embodiment; [0075] Figures 20A and 20B are process flow diagrams of certain process steps of
  • Figure 11 for rendering a light field originating from multiple distinct virtual image planes, in accordance with one embodiment
  • Figures 21 A and 21 B are process flow diagrams of certain process steps of Figures 20 A and 20B for rendering a light field originating from multiple distinct virtual image planes, in accordance with one embodiment;
  • Figures 22A to 22D are schematic diagrams illustrating certain process steps of Figures 21 A and 2 IB, in accordance with one embodiment;
  • Figures 23 A and 23B are process flow diagrams of certain process steps of Figure 11 for rendering a light field originating from multiple distinct focal planes, in accordance with one embodiment
  • Figures 24A and 24B are schematic diagrams illustrating an example of a subjective visual acuity test using the ray-tracing rendering process of Figures 23A or Figure 23B, in accordance with one embodiment
  • Figure 25 is a schematic diagram of an exemplary virtual phase element for simulating optical aberrations, including higher order aberrations (HO As), in accordance with one embodiment
  • Figures 26A and 26B are schematic diagrams illustrating how a phase element of Figure 25 may be used to simulate aberrations, including HO As, in the eye (26A) or in a phase element located in front of the eye (20B), in accordance with one embodiment;
  • Figures 27A to 27D are schematic diagrams illustrating different exemplary shapes or profiles of the phase element of Figure 25, in accordance with one embodiment;
  • Figure 28 is a schematic diagram illustrating a side-view of an exemplary phase element comprising a variable profile defined via a height or thickness function, in accordance with one embodiment
  • Figure 29 is a process flow diagram of an illustrative ray -tracing rendering process using the phase element of Figure 25 and operable to compensate for HOAs, in accordance with one embodiment
  • Figure 30 is process flow diagram illustrating certain process steps of Figure 29, in accordance with one embodiment
  • Figures 31 A and 3 IB are process flow diagrams illustrating certain process steps of Figure 30, in accordance with one embodiment
  • Figures 32A and 32B are plots of different profiles comparison of normally incident beam for raytracing through phase elements of Figure 25 compared to diffraction with the corresponding aberration phase added to the wave front pre-diffraction. Normalized intensity profiles at the detector/image plane are shown, in accordance with one embodiment;
  • Figure 33 A and 33B are exemplary plots of a height or thickness function for a phase element simulating astigmatism, in accordance with one embodiment
  • Figure 34 is a schematic diagram illustrating certain process steps of Figures 35 and 38, in accordance with one embodiment;
  • Figure 35 is a process flow diagram illustrating certain process steps of Figure
  • Figures 36A to 36C are schematic diagrams illustrating certain process steps of Figures 35, in accordance with one embodiment
  • Figures 37A to 37C are schematic diagrams illustrating a phase element defined as a pre-computed set of height values and normal vectors, in accordance with one embodiment
  • Figure 38 is a process flow diagram illustrating certain process steps of Figure 29, in accordance with one embodiment
  • Figure 39 is a process flow diagram of an illustrative ray -tracing rendering process for rendering simultaneously multiple images or optotypes compensating for different sets of HO As, in accordance with one embodiment
  • Figures 40A and 40B are process flow diagrams illustrating certain process steps of Figure 39, in accordance with one embodiment
  • Figure 41 is a process flow diagram illustrating certain process steps of Figure 40A, in accordance with one embodiment
  • Figure 42 is a process flow diagram illustrating certain process steps of Figure 40B, in accordance with one embodiment
  • Figure 43 is a process flow diagram illustrating certain process steps of Figure 40B, in accordance with one embodiment.
  • Figure 44 is a schematic diagram illustrating the use of multiple phase elements simultaneously, in accordance with one embodiment;
  • Figure 45 is a process flow diagram illustrating an exemplary unified light field rendering method incorporating phase elements, in accordance with one embodiment.
  • Figure 46 is a schematic diagram illustrating certain process steps of the method of Figure 45, in accordance with one embodiment.
  • elements may be described as “configured to” perform one or more functions or “configured for” such functions.
  • an element that is configured to perform or configured for performing a function is enabled to perform the function, or is suitable for performing the function, or is adapted to perform the function, or is operable to perform the function, or is otherwise capable of performing the function.
  • the methods and systems described herein are directed, according to different embodiments, to light field rendering methods and systems capable of compensating for, or simulating, the presence of one or more optical aberrations, including higher order aberrations (HO As), in, or disposed in relation to, a user’s eye so to present a corrected, simulating or compensating image thereto.
  • optical aberrations including higher order aberrations (HO As)
  • HO As higher order aberrations
  • the methods and systems discussed below, in accordance with different embodiments make use of a “virtual” optical element or phase element specifically tailored or defined so as to correctly reproduce or simulate the presence of these one or more aberrations.
  • a higher order aberration as compared to lower zero, first or second-order aberrations, can often be defined by one or more polynomial functions that, alone or in combination, can be used to define a refractive response resulting from the higher order aberration.
  • higher order aberrations may include, but are not limited to, trefoil, coma, and spherical aberrations that may result in poor night vision, glare, halos, blurring, starburst patterns or double vision.
  • lower order aberrations such as those common to astigmatism (e.g. defined by cylindrical and axis parameters), myopia or hyperopia (e.g.
  • addressed aberrations may be decomposed into lower and/or higher order aberrations as defined by respective or combined aberration parameters, whereby some may be otherwise addressed by alternate methods (e.g. within the simplified context of lower order aberrations), whereas other aberrations may be defined by complementary aberration parameters (e.g. higher order aberration parameters, etc.) and specifically addressed by the methods and approaches described herein. As such, in combination, all aberration parameters may be effectively addressed or simulated.
  • devices, displays and methods described herein may allow a user’s perception of one or more input images (or input image portions), where each image or image portion is virtually located or perceived to be at a distinct image plane/depth location, to be adjusted or altered using the described light field display technology, again allowing for corrective assessment and/or previewing capabilities in respect of this viewer’s reduced visual acuity or aberrations.
  • Some of the herein described embodiments provide for digital display devices, or devices encompassing such displays, for use by users having reduced visual acuity, whereby images ultimately rendered by such devices can be dynamically processed to accommodate the user’s reduced visual acuity so that they may more comfortably consume rendered images without the use of corrective eyewear, contact lenses, or surgical intervention, as would otherwise be required.
  • embodiments are not to be limited as such as the notions and solutions described herein may also be applied to other technologies in which a user’s perception of an input image to be displayed can be altered or adjusted via the light field display.
  • digital displays as considered herein will comprise a set of image rendering pixels and a corresponding set of light field shaping elements that at least partially govern a light field emanated thereby to produce a perceptively adjusted version of the input image, notably distinct perceptively adjusted portions of an input image or input scene, which may include distinct portions of a same image, a same 2.5D/3D scene, or distinct images (portions) associated with different image depths, effects and/or locations and assembled into a combined visual input.
  • light field shaping elements may take the form of a light field shaping layer or like array of optical elements to be disposed relative to the display pixels in at least partially governing the emanated light field.
  • such light field shaping layer elements may take the form of a microlens and/or pinhole array, or other like arrays of optical elements, or again take the form of an underlying light field shaping layer, such as an underlying array of optical gratings or like optical elements operable to produce a directional pixelated output.
  • the light field shaping layer can be disposed at a pre-set distance from the pixelated display so to controllably shape or influence a light field emanating therefrom.
  • each light field shaping layer can be defined by an array of optical elements centered over a corresponding subset of the display’s pixel array to optically influence a light field emanating therefrom and thereby govern a projection thereof from the display medium toward the user, for instance, providing some control over how each pixel or pixel group will be viewed by the viewer’s eye(s).
  • arrayed optical elements may include, but are not limited to, lenslets, microlenses or other such diffractive optical elements that together form, for example, a lenslet array; pinholes or like apertures or windows that together form, for example, a parallax or like barrier; concentrically patterned barriers, e.g. cut outs and/or windows, such as a to define a Fresnel zone plate or optical sieve, for example, and that together form a diffractive optical barrier (as described, for example, in Applicant’s co- pending U.S. Application Serial No.
  • a lenslet array whose respective lenses or lenslets are partially shadowed or barriered around a periphery thereof so to combine the refractive properties of the lenslet with some of the advantages provided by a pinhole barrier.
  • the display device will also generally invoke a hardware processor operable on image pixel (or subpixel) data for an image to be displayed to output corrected or adjusted image pixel data to be rendered as a function of a stored characteristic of the light field shaping elements and/or layer (e.g. layer distance from display screen, distance between optical elements (pitch), absolute relative location of each pixel or subpixel to a corresponding optical element, properties of the optical elements (size, diffractive and/or refractive properties, etc.), or other such properties, and a selected vision correction or adjustment parameter related to the user’s reduced visual acuity or intended viewing experience.
  • a hardware processor operable on image pixel (or subpixel) data for an image to be displayed to output corrected or adjusted image pixel data to be rendered as a function of a stored characteristic of the light field shaping elements and/or layer (e.g. layer distance from display screen, distance between optical elements (pitch), absolute relative location of each pixel or subpixel to a corresponding optical element, properties of the optical elements (size, diffractive and
  • image processing can, in some embodiments, be dynamically adjusted as a function of the user’s visual acuity or intended application so to actively adjust a distance of a virtual image plane, or perceived image on the user’s retinal plane given a quantified user eye focus or like optical aberration(s), induced upon rendering the corrected/adjusted image pixel data via the static optical layer and/or elements, for example, or otherwise actively adjust image processing parameters as may be considered, for example, when implementing a viewer-adaptive pre-filtering algorithm or like approach (e.g. compressive light field optimization), so to at least in part govern an image perceived by the user’s eye(s) given pixel or subpixel-specific light visible thereby through the layer.
  • a viewer-adaptive pre-filtering algorithm or like approach e.g. compressive light field optimization
  • a corrective vision previewing device/system (interchangeably referred to as a corrective vision previewing device/system), generally referred to using the numeral 100, will now be described.
  • a light field vision testing device such as a light field refractor or phoropter device 102.
  • light field refractor 102 is a device comprising, as mentioned above, a light field display 104 and which is operable to display or generate one or more images, including optotypes, to a user or patient having his/her vision acuity (e.g. refractive error) tested.
  • light field display 104 comprises a light field shaping layer (LFSL) 108 overlaid or placed in front of a digital pixel display 110 (i.e. LCD, LED, OLED, etc.).
  • LFSL light field shaping layer
  • digital pixel display 110 i.e. LCD, LED, OLED, etc.
  • a lenslet array comprising an array of microlenses (also interchangeably referred to herein as lenslets) that are each disposed at a distance from a corresponding subset of image rendering pixels in an underlying digital display.
  • a light field shaping layer may be manufactured and disposed as a digital screen overlay
  • other integrated concepts may also be considered, for example, where light field shaping elements are integrally formed or manufactured within a digital screen’s integral components such as a textured or masked glass plate, beam-shaping light sources (e.g. directional light sources and/or backlit integrated optical grating array) or like component.
  • each lenslet will predictively shape light emanating from these pixel subsets to at least partially govern light rays being projected toward the user by the display device.
  • other light field shaping layers may also be considered herein without departing from the general scope and nature of the present disclosure, whereby light field shaping will be understood by the person of ordinary skill in the art to reference measures by which light, that would otherwise emanate indiscriminately (i.e. isotropically) from each pixel group, is deliberately controlled to define predictable light rays that can be traced between the user and the device’s pixels through the shaping layer.
  • a light field is generally defined as a vector function that describes the amount of light flowing in every direction through every point in space. In other words, anything that produces or reflects light has an associated light field.
  • the embodiments described herein produce light fields from an object that are not “natural” vector functions one would expect to observe from that object. This gives it the ability to emulate the “natural” light fields of objects that do not physically exist, such as a virtual display located far behind the light field display.
  • a light field display 104 projects the correct sharp image (H) on the retina for an eye with a crystalline lens which otherwise could not accommodate sufficiently to produce a sharp image.
  • the other two light field pixels (I) and (J) are drawn lightly, but would otherwise fill out the rest of the image.
  • a light field as seen in Figure 2C cannot be produced with a ‘normal’ two-dimensional display because the pixels’ light field emits light isotopically. Instead it is necessary to exercise tight control on the angle and origin of the light emitted, for example, using a microlens array or other light field shaping layer such as a parallax barrier, or combination thereof.
  • Figure 3A schematically illustrates a single light field pixel defined by a convex microlens 302 disposed at its focus from a corresponding subset of pixels in a digital pixel display 108 to produce a substantially collimated beam of light emitted by these pixels, whereby the direction of the beam is controlled by the location of the pixel(s) relative to the microlens.
  • the single light field pixel produces a beam similar to that shown in Figure 2C where the outside rays are lighter and the majority inside rays are darker.
  • the digital pixel display 108 emits light which hits the microlens 302 and it results in a beam of substantially collimated light (A).
  • FIG. 3B schematically illustrates an example of a light field display assembly in which a LFSL 106 sits above a pixel display 108 to have pixels 304 emit light through the microlens array.
  • a ray -tracing algorithm can thus be used to produce a pattern to be displayed on the pixel array below the microlens in order to create the desired virtual image that will effectively correct for the viewer’s reduced visual acuity.
  • the separation between the LFSL 106 and the pixel array 108 as well as the pitch of the lenses can be selected as a function of various operating characteristics, such as the normal or average operating distance of the display, and/or normal or average operating ambient light levels.
  • LFSL 106 may be a microlens array (MLA) defined by a hexagonal array of microlenses or lenslet disposed so to overlay a corresponding square pixel array of digital pixel display 108.
  • MLA microlens array
  • each microlens can be aligned with a designated subset of pixels to produce light field pixels as described above, the hexagonal-to-square array mismatch can alleviate certain periodic optical artifacts that may otherwise be manifested given the periodic nature of the optical elements and principles being relied upon to produce the desired optical image corrections.
  • a square microlens array may be favoured when operating a digital display comprising a hexagonal pixel array.
  • the MLA may further or alternatively be overlaid or disposed at an angle (rotation) relative to the underlying pixel array, which can further or alternatively alleviate period optical artifacts.
  • a pitch ratio between the microlens array and pixel array may be deliberately selected to further or alternatively alleviate periodic optical artifacts. For example, a perfectly matched pitch ratio (i.e. an exact integer number of display pixels per microlens) is most likely to induce periodic optical artifacts, whereas a pitch ratio mismatch can help reduce such occurrences.
  • the pitch ratio will be selected to define an irrational number, or at least, an irregular ratio, so to minimize periodic optical artifacts.
  • a structural periodicity can be defined so to reduce the number of periodic occurrences within the dimensions of the display screen at hand, e.g. ideally selected so to define a structural period that is greater than the size of the display screen being used.
  • light field display 104 can render dynamic images at over 30 frames per second on the hardware in a smartphone.
  • a display device as described above and further exemplified below can be configured to render a corrected or adjusted image via the light field shaping layer that accommodates, tests or simulates for the user’s visual acuity.
  • light field rendering may be adjusted to effectively generate a virtual image on a virtual image plane that is set at a designated distance from an input user pupil location, for example, so to effectively push back, or move forward, a perceived image, or portion thereof, relative to the light field refractor device 102.
  • light field rendering may rather or alternatively seek to map the input image on a retinal plane of the user, taking into account visual aberrations, so to adaptively adjust rendering of the input image on the display device to produce the mapped effect.
  • the unadjusted input image would otherwise typically come into focus in front of or behind the retinal plane (and/or be subject to other optical aberrations)
  • this approach allows to map the intended image on the retinal plane and work therefrom to address designated optical aberrations accordingly.
  • the device may further computationally interpret and compute virtual image distances tending toward infinity, for example, for extreme cases of presbyopia.
  • This approach may also more readily allow, as will be appreciated by the below description, for adaptability to other visual aberrations that may not be as readily modeled using a virtual image and image plane implementation.
  • the input image is digitally mapped to an adjusted image plane (e.g. virtual image plane or retinal plane) designated to provide the user with a designated image perception adjustment that at least partially addresses designated visual aberrations.
  • an adjusted image plane e.g. virtual image plane or retinal plane
  • the light field display is able to generate displacements (line 502) in diopters that have higher resolution corresponding to 20/20 vision (line 504) or better (e.g. 20/15 - line 506) and close to (20/10 - line 508)), here within a dioptric power range of 2 to 2.5 diopters.
  • light field display 104 may, according to different embodiments, be used to replace, at least in part, traditional optical components.
  • the light field display can display a virtual image at optical infinity, meaning that any level of accommodation-based presbyopia (e.g. first order) can be corrected for.
  • the light field display can both push the image back or forward, thus allowing for selective image corrections for both hyperopia (far-sightedness) and myopia (nearsightedness).
  • variable displacements and/or accommodations may be applied as a function of non-uniform visual aberrations, or again to provide perceptive previewing or simulation of non-uniform or otherwise variable corrective powers/measures across a particular input or field of view.
  • the light field rendering system introduced above and the ray -tracing methods described below may also be used with other devices which may similarly comprise a light field display.
  • this may include a smartphone, tablets, e- readers, watches, televisions, GPS devices, laptops, desktop computer monitors, televisions, smart televisions, handheld video game consoles and controllers, vehicular dashboard and/or entertainment displays, and the like, without limitation.
  • any of the light field processing or ray -tracing methods described below, any modification thereto also discussed below, and related light field display solutions can be equally applied to image perception adjustment solutions for visual media consumption, as they can for subjective vision testing solutions, or other technologically related fields of endeavour.
  • the light field display and rendering/ray- tracing methods discussed above may all be used to implement, according to various embodiments, a subjective vision testing device or system such as a phoropter or refractor.
  • a light field display may replace, at least in part, the various refractive optical components usually present in such a device.
  • vision correction light field ray tracing methods discussed below may equally be applied to render optotypes at different dioptric power or refractive correction by generating vision correction for hyperopia (far- sightedness) and myopia (nearsightedness), as was described above in the general case of a vision correction display.
  • Light field systems and methods described herein, according to some embodiments, may be applied to create the same capabilities as a traditional instrument and to open a spectrum of new features, all while improving upon many other operating aspects of the device.
  • the digital nature of the light field display enables continuous changes in dioptric power compared to the discrete change caused by switching or changing a lens or similar; displaying two or more different dioptric corrections seamlessly at the same time; and, in some embodiments, the possibility of measuring higher-order aberrations and/or to simulate them for different purposes such as, deciding for free-form lenses, cataract surgery operation protocols, IOL choice, etc.
  • a correct light field can be produced, in some embodiments, only at or around the location of the user’s pupil(s).
  • the light field display can be paired with pupil tracking technology, as will be discussed below, to track a location of the user’s eyes/pupils relative to the display. The display can then compensate for the user’s eye location and produce the correct virtual image, for example, in real-time.
  • light field refractor 102 may include, integrated therein or interfacing therewith, a pupil/eye tracking system 110 to improve or enhance corrective image rendering by tracking a location of the user’s eye(s)/pupil(s) (e.g. both or one, e.g. dominant, eye(s)) and adjusting light field corrections accordingly one or more eye/pupil tracking light sources, such as one or more infrared (IR) or near-IR (NIR) light source(s) to accommodate operation in limited ambient light conditions, leverage retinal retro- reflections, invoke corneal reflection, and/or other such considerations.
  • IR/NIR pupil tracking techniques may employ one or more (e.g.
  • IR/NIR IR-based machine vision and facial recognition techniques
  • Other techniques may employ ambient or IR/NIR light-based machine vision and facial recognition techniques to otherwise locate and track the user’s eye(s)/pupil(s).
  • one or more corresponding (e.g. visible, IR/NIR) cameras may be deployed to capture eye/pupil tracking signals that can be processed, using various image/sensor data processing techniques, to map a 3D location of the user’s eye(s)/pupil(s).
  • eye/pupil tracking hardware/software may be integral to device 102, for instance, operating in concert with integrated components such as one or more front facing camera(s), onboard IR/NIR light source(s) (not shown) and the like.
  • eye/pupil tracking hardware may be further distributed within the environment, such as dash, console, ceiling, windshield, mirror or similarly-mounted camera(s), light sources, etc.
  • light field refractor 102 may be configured with light field display 104 located relatively far away (e.g. one or more meters) from the user’s eye currently being diagnosed.
  • the pointed line in Figures 4A to 4C is used to schematically illustrate the direction of the light rays emitted by light field display 104.
  • eye-tracker 110 which may be provided as a physically separate element, for example, installed in at a given location in a room or similar.
  • the noted eye/pupil tracker 110 may include the projection of IR marker s/patterns to help align the patient’s eye with the light field display.
  • a tolerance window e.g.
  • eye box may be considered to limit the need to refresh the ray-tracing iteration.
  • An exemplary value of the size of the eye box in some embodiments, is around 6 mm, though smaller (e.g. 4mm) or larger eye boxes may alternatively be set to impact image quality, stability or like operational parameters.
  • light field refractor 102 may also comprise, according to different embodiments and as will be further discussed below, one or more refractive optical components 112, a processing unit 114, a data storage unit or internal memory 116, one or more cameras 118, a power source 120, a network interface 122 for communicating via network to a remote database or server 124.
  • power source 120 may comprise, for example, a rechargeable Li-ion battery or similar. In some embodiments, it may comprise an additional external power source, such as, for example, a USB-C external power supply. It may also comprise a visual indicator (screen or display) for communicating the device’s power status, for example whether the device is on/off or recharging.
  • internal memory 116 may be any form of electronic storage, including a disk drive, optical drive, read-only memory, random-access memory, or flash memory, to name a few examples.
  • a library of chart patterns may be located in internal memory 116 and/or retrievable from remote server 124 via network interface 122.
  • one or more optical components 112 may be used in combination with the light field display 104, for example to shorten the size of refractor 102 and still offer an acceptable range in dioptric power.
  • the general principle is schematically illustrated in the plots of Figures 6A to 6D. In these schematic plots, the image quality (e.g. inverse of the angular resolution, higher is better) at which optotypes are small enough to be useful for vision testing in this plot is above horizontal line 602 which represents typical 20/20 vision.
  • Figure 6A shows the plot for the light field display only, where we see the characteristic two peaks corresponding to the smallest resolvable point, one of which was plotted in Figure 5 (here inverted and shown as a peak instead of a basin), and where each region above the line may cover a few diopters of dioptric power, according to some embodiments. While the dioptric range may, in some embodiments, be more limited than needed when relying only on the light field display, it is possible to shift this interval by adding one or more refractive optical components. This is shown in Figure 6B where the regions above the line 602 is shifted to the left (negative diopters) by adding a single lens in the optical path.
  • light field refractor 102 is schematically illustrated in Figure 4B, wherein the light field display 104 (herein shown comprising LFSL 106 and digital pixel display 108) is combined with a multiplicity of refractive components 112 (herein illustrated as a reel of lenses as an example only).
  • the refractive component used in combination with light field display 104 By changing the refractive component used in combination with light field display 104, a larger dioptric range may be covered. This may also provide means to reduce the dimension of device 102 as mentioned above, making it more portable, so that all its internal components may be encompassed into a shell, housing or casing 402.
  • light field refractor 102 may thus comprise a durable ABS housing that may be shock and harsh-environment resistant.
  • light field refractor 102 may also comprise a telescopic feel for fixed or portable usage; optional mounting brackets, and/or a carrying case (not shown). In some embodiments, all components may be internally protected and sealed from the elements.
  • casing 402 may further comprise a head-rest or similar (not shown) to keep the user’s head still and substantially in the same location, thus, in such examples, foregoing the general utility of a pupil tracker or similar techniques by substantially fixing a pupil location relative to this headrest.
  • refractive components 112 may be include, without limitation, one or more lenses, sometimes arranged in order of increasing dioptric power in one or more reels of lenses similar to what is typically found in traditional refractors/phoropters; an electrically controlled fluid lens; active Fresnel lens; and/or Spatial Light Modulators (SLM).
  • additional motors and/or actuators may be used to operate refractive components 112.
  • the motor s/actuators may be communicatively linked to processing unit 114 and power source 120, and operate seamlessly with light field display 102 to provide the required dioptric power.
  • Figures 7A and 7B show a perspective view of an exemplary light field phoropter 102 similar to the one schematically shown in Figure 3B, but wherein the refractive component 112 is an electrically tunable liquid lens.
  • the electrically tunable lens may have a range of ⁇ 13 diopters.
  • a 1000 dpi display is used with a MLA having a 65 mm focal distance and 1000 pm pitch with the user’s eye located at a distance of about 26 cm.
  • a similar embodiment uses the same MLA and user distance with a 3000 dpi display.
  • eye-tracker 110 may further comprise a digital camera, in which case it may be used to further acquire images of the user’s eye to provide further diagnostics, such as pupillary reflexes and responses during testing for example.
  • one or more additional cameras 118 may be used to acquire these images instead.
  • light field refractor 102 may comprise built-in stereoscopic tracking cameras.
  • control interface 126 may comprise a dedicated handheld controller-like device 128.
  • This controller 128 may be connected via a cable or wirelessly, and may be used by the patient directly and/or by an operator like an eye professional.
  • both the patient and operator may have their own dedicated controller 128.
  • the controller may comprise digital buttons, analog thumbstick, dials, touch screens, and/or triggers.
  • control interface 126 may comprise a digital screen or touch screen, either on refractor 102 itself or part of an external module (not shown).
  • control interface 126 may let on or more external remote devices (i.e. computer, laptop, tablet, smartphone, remote, etc.) control light field refractor 102 via network interface 122.
  • remote digital device 130 may be connected to light field refractor 102 via a cable (e.g. USB cable, etc.) or wirelessly (e.g. via Wi-Fi, Bluetooth or similar) and interface with light field refractor 102 via a dedicated application, software or website (not shown).
  • a dedicated application may comprise a graphical user interface (GUI), and may also be communicatively linked to remote database 124.
  • GUI graphical user interface
  • the user or patient may give feedback verbally and the operator may control the vision test as a function of that verbal feedback.
  • refractor 102 may comprise a microphone (not shown) to record the patient’ s verbal communications, either to communicate them to a remote operator via network interface 122 or to directly interact with the device (e.g. via speech recognition or similar).
  • processing unit 114 may be communicatively connected to data storage 116, eye tracker 110, light field display 104 and refractive components 112. Processing unit 114 may be responsible for rendering one or more images or optotypes via light field display 104 and, in some embodiments, jointly control refractive components 112 to achieve a required total change in dioptric power. It may also be operable to send and receive data to internal memory 116 or to/from remote database 124 via network interface 122.
  • diagnostic data may be automatically transmitted/communicated to remote database 124 or remote digital device 130 via network interface 122 through the use of a wired or wireless network connection.
  • a wired or wireless network connection may be considered herein, such as, but not limited to, Wi-Fi, Bluetooth, NFC, Cellular, 2G, 3G, 4G, 5G or similar.
  • the connection may be made via a connector cable (e.g. USB including microUSB, USB-C, Lightning connector, etc.).
  • remote digital device 130 may be located in a different room, building or city.
  • two light field refractors 102 may be combined side-by- side to independently measure the visual acuity of both left and right eye at the same time.
  • An example is shown in Figure 7C, where two units corresponding to the embodiment of Figures 7A or 7B (used as an example only) are placed side-by-side or fused into a single device.
  • a dedicated application, software or website may provide integration with third party patient data software.
  • software required to operate and installed on refractor 102 may be updated on-the-fly via a network connection and/or be integrated with the patient’s smartphone app for updates and reminders.
  • the dedicated application, software or website may further provide a remote, real-time collaboration platform between an eye professional and user/patient, and/or between different eye professionals. This may include interaction between different participants via video chat, audio chat, text messages, etc.
  • light field refractor 102 may be self-operated or operated by an optometrist, ophthalmologist or other certified eye-care professional.
  • a user/patient may use refractor 102 in the comfort of his/her own home, in a store or a remote location.
  • a dynamic subjective vision testing method using vision testing system 100 generally referred to using the numeral 800, will now be described.
  • method 800 seeks to diagnose a patient’s reduced visual acuity and produce therefrom, in some embodiments, an eye prescription or similar.
  • eye prescription information may include, for each eye, one or more of: distant spherical, cylindrical and/or axis values, and/or a near (spherical) addition value.
  • the eye prescription information may also include the date of the eye exam and the name of the eye professional that performed the eye exam.
  • the eye prescription information may also comprise a set of vision correction parameter(s), as will be further discussed below, for operating any vision correction light field displays using the systems and methods described below.
  • the eye prescription may be tied to a patient profile or similar, which may contain additional patient information such as a name, address or similar. The patient profile may also contain additional medical information about the user. All information or data (i.e. set of vision correction parameter(s), user profile data, etc.) may be kept on external database 124.
  • the user’s current vision correction parameter(s) may be actively stored and accessed from external database 124 operated within the context of a server-based vision correction subscription system or the like, and/or unlocked for local access via the client application post user authentication with the server- based system.
  • Refractor 102 being, in some embodiments, portable, a large range of environments may be chosen to deliver the vision test (home, eye practitioner’s office, etc.).
  • the patient’s eye may be placed at the required location. This may be done by placing his/her head on a headrest or by placing the objective (i.e. eyepiece) on the eye to be diagnosed.
  • the vision test may be self-administered or partially self-administered by the patient.
  • the operator e.g. eye professional or other
  • the operator may have control over the type of test being delivered, and/or be the person who generates or helps generate therefrom an eye prescription, while the patient may enter inputs dynamically during the test (e.g.
  • a location is acquired.
  • such a pupil location may be acquired via eye tracker 110, either once, at intervals, or continuously.
  • the location may be derived from the device or system’s dimension.
  • the use a head-rest and/or an eye-piece or similar provides an indirect means of deriving the pupil location.
  • refractor 102 may be self-calibrating and not require any additional external configuration or manipulation from the patient or the practitioner before being operable to start a vision test.
  • one or more optotypes is/are displayed to the patient, at one or more dioptric power (e.g. in sequence, side-by-side, or in a grid pattern/layout).
  • the use of light field display 104 offers multiple possibilities regarding how the images/optotypes are presented, and at which dioptric power each may be rendered.
  • the optotypes may be presented sequentially at different dioptric power, via one or more dioptric power increments.
  • the patient and/or operator may control the speed and size of the dioptric power increments.
  • optotypes may also be presented, at least in part, simultaneously on the same image but rendered at a different dioptric power.
  • Figure 9 shows an example of how different optotypes may be displayed to the patient but rendered with different dioptric powers simultaneously. These may be arranged in columns or in a table or similar. In Figure 9, we see two columns of three optotypes (K, S, V), varying in size, as they are perceived by a patient, each column being rendered at different degrees of refractive correction (e.g. dioptric power). In this specific example, the optotypes on the right are being perceived as blurrier than the optotypes on the left.
  • method 800 may be configured to implement dynamic testing functions that dynamically adjust one or more displayed optotype’s dioptric power in real-time in response to a designated input, herein shown by the arrow going back from step 808 to step 804 in the case where at step 808, the user or patient communicates that the perceived optotypes are still blurry or similar.
  • the patient may indicate when the optotypes shown are clearer.
  • the patient may control the sequence of optotypes shown (going back and forth as needed in dioptric power), and the speed and increment at which these are presented, until he/she identifies the clearest optotype.
  • the patient may indicate which optotype or which group of optotypes is the clearest by moving an indicator icon or similar within the displayed image.
  • the optotypes may be presented via a video feed or similar.
  • step 804 may in this case comprise first displaying larger increments of dioptric power by changing lens as needed, and when the clearest or less blurry optotypes are identified, fine-tuning with continuous or smaller increments in dioptric power using the light field display.
  • the refractive components 112 may act on all optotypes at the same time, and the change in dioptric power between them may be controlled only by the light display 104.
  • the change in dioptric power may be continuous.
  • eye images may be recorded during steps 802 to 806 and analyzed to provide further diagnostics.
  • eye images may be compared to a bank or database of proprietary eye exam images and analyzed, for example via an artificial intelligence (AI) or Machine-learning (ML) system or similar. This analysis may be done by refractor 102 locally or via a remote server or database 124.
  • AI artificial intelligence
  • ML Machine-learning
  • an eye prescription or vision correction parameter(s) may be derived from the total dioptric power used to display the best perceived optotypes.
  • the patient, an optometrist or other eye-care professional may be able to transfer the patient’s eye prescription directly and securely to his/her user profile store on said server or database 124. This may be done via a secure website, for example, so that the new prescription information is automatically uploaded to the secure user profile on remote database 124.
  • the eye prescription may be sent remotely to a lens specialist or similar to have prescription glasses prepared.
  • vision testing system 100 may also or alternatively be used to simulate compensation for other or higher-order aberrations.
  • the light field rendering methods described above may be used to compensation for higher order aberrations (HO A), and thus be used to validate externally measured or tested HOA via method 3600, in that a measured, estimated or predicted HOA can be dynamically compensated for using the system described herein and thus subjectively visually validated by the viewer in confirming whether the applied HOA correction satisfactorily addresses otherwise experienced vision deficiencies.
  • an exemplary computationally implemented ray-tracing method for rendering an adjusted image via an array of light field shaping elements in this example provided by a light field shaping layer (LFSL) disposed relative to a set of underlying display pixels, that accommodates or compensates for the user’s reduced visual acuity
  • LFSL light field shaping layer
  • this first example for illustrative purposes, adjustment of a single image (i.e. the image as whole) is being implemented without consideration for distinct image portions and taking only into account spherical dioptric power changes. Further examples below will specifically address modification of the following example for adaptively adjusting distinct image portions and/or adjustments considering other aberrations such as HO A, and/or astigmatism.
  • a set of constant parameters 1002 used for the light field rendering process may be pre-determined. These may include, for example, any data or parameters that are not expected to significantly change during a user’s viewing session, between different viewing sessions or even between users, for instance. These may generally be based on the physical and functional characteristics of light field display 104 for which the method is to be implemented, as will be explained below.
  • every iteration of the rendering algorithm i.e. when rendering a full light field image frame
  • the list of constant parameters 1002 may include, without limitations, the distance 1006 between pixel display 108 and the LFSL 106, the in- plane rotation angle 1008 between the frames of reference digital pixel display 108 and LFSL 106, the resolution 1010 and/or size 1011 of digital pixel display 108, the size 1012 of each individual pixel, the optical geometry 1014 of LFSL 106, the size or pitch of individual optical elements or units 1016 within LFSL 106 and optionally the subpixel layout 1018 of pixel display 108.
  • both the resolution 1010 and the size of each individual pixel 1012 of pixel display 108 may be used to pre-determine both the absolute size of the display in real units (i.e.
  • the position/location within pixel display 108 of each subpixel may also be pre- determined.
  • These three-dimensional location/positions are usually calculated using a given frame of reference located somewhere within the plane of pixel display 108, for example a corner or the middle of the display, although other reference points may be chosen.
  • Concerning the optical layer geometry 1014 different geometries may be considered, for example a hexagonal geometry.
  • Figure 10B meanwhile illustratively lists an exemplary set of input variables 1004 that may be used for the light field rendering methods described below, and may include any input data that may reasonably change during a user’s single viewing session, for example between each image frame, or between different viewing sessions or even between different users (e.g. not related to the hardware specifications of light field display 104 or refractor 102).
  • These may be automatically acquired by device 102 during normal operation or be inputted (for example by a user or person operating the device for the user) into the device as required. They may thus include without limitation: the image(s)/optotype(s) to be displayed 1020 (e.g. comprising pixel data such as on/off, colour, brightness, etc.), a three-dimensional pupil center location 1022 (e.g. in embodiments implementing active eye/pupil tracking methods) and/or a pupil size 1024.
  • the image(s)/optotype(s) to be displayed 1020 e.g. comprising pixel data such as on/off
  • vision correction parameters in the form of dioptric power so as to modulate the strength and nature of the compensation/correction generated by the light field image.
  • These may include a spherical dioptric power 1026 (which may be derived indirectly, for example, from a minimum reading distance value 1028 as will be discussed below), but also, in some embodiments, one or more sets of a cylindrical power 1030 and a corresponding cylindrical axis angle 1032.
  • these input variables (spherical dioptric power 1026, cylindrical dioptric power 1026 and cylinder axis angle 1030) mirror the SPHERE,
  • CYL and AXIS parameters used in a typical eye examination.
  • an eye depth value 1034 may also be used, either as an average value or customized for an individual user.
  • input image 1020 may be representative of one or more digital images to be displayed with digital pixel display 108.
  • input image 1020 may generally be encoded in any data format used to store digital images known in the art.
  • Pupil center location 1022 is the three-dimensional coordinates of at least one the user’s pupils’ center with respect to a given reference frame, for example a point on device 102 or digital pixel display 108 and may be derived from any eye/pupil tracking method known in the art via eye/pupil tracker 110.
  • the pupil center location 1022 may be determined prior to any new iteration of the rendering algorithm, or in other cases, at a lower framerate (and thus re-use the same location/position for two or more subsequent image frames).
  • only the pupil center location of a single user’s eye may be determined, for example the user’s dominant eye (i.e. the one that is primarily relied upon by the user).
  • this location/position, and particularly the associated pupil distance to the screen may otherwise or additionally be rather approximated or adjusted based on other contextual or environmental parameters, such as an average or preset user distance to the screen (e.g. typical reading distance for a given user or group of users; stored, set or adjustable driver distance in a vehicular environment; etc.).
  • other contextual or environmental parameters such as an average or preset user distance to the screen (e.g. typical reading distance for a given user or group of users; stored, set or adjustable driver distance in a vehicular environment; etc.).
  • the minimum reading distance 1028 is defined as the minimal focus distance for reading that the user’ s eye(s) may be able to accommodate (i.e. able to view without discomfort).
  • different values of the minimum reading distance 1028 associated with different users may be entered, for example, as can other adaptive vision correction parameters be considered depending on the application at hand and vision correction being addressed.
  • minimum reading distance 1028 may be derived from an eye prescription (e.g. glasses prescription or contact prescription) or similar. It may, for example, correspond to the near point distance corresponding to the uncorrected user’s eye, which can be calculated from the prescribed corrective lens power assuming that the targeted near point was at 25 cm.
  • input variables 1004 may further comprise a set of Zernike coefficients 1036. These are usually used to define or characterize a set of HO As to be corrected, as will be described below, in accordance with different embodiments. These may be chosen so as to describe one or more optical aberrations via a Zernike polynomial. In some embodiments, these may be used in addition to or in replacement of previously discussed variables such as spherical power 1026, cylindrical power 1030 or cylinder axis angle 1032. In other embodiments, at least some of the Zernike coefficients 1036 may be derived from spherical power 1026, cylindrical power 1030 or cylinder axis angle 1032.
  • Zernike coefficients 1036 may be used to model HOA only, while spherical power may be simulated via the method 1100 described below.
  • the corresponding Zernike coefficients 1036 may be computed from spherical power 1026, cylindrical power 1030 or cylinder axis angle 1032, as will be shown below.
  • an optical or phase element to simulate the effects of HO As.
  • This element may have additional variables associated with it, for example at least one refractive index 1038 and a location/orientation 1040. More details regarding the use of this phase element (or a plurality of elements) will be given further below.
  • parameters 1002 and variables 1004 may be used in the light field ray -tracing method 1100, herein presented in accordance with different embodiments. While method 1100 and the steps described in Figure 12 apply equally to both embodiments, steps 1102 and 1112 may be applied using either virtual image planes “virtually” located behind the display or on the retinal plane (via an eye focal plane (i.e. inside the eye)).
  • method 1100 as illustrated in Figures 11 to 17D is designed to correct for spherical aberrations.
  • other methods expanding on method 1100 for example that may also correct for astigmatism, will be described further below.
  • method 1100 begins with step 1102, in which the image to be displayed is pre-processed for subsequent ray-tracing steps. This includes numerically computing a location or position for a corresponding adjusted image surface or plane that corresponds to the required spherical dioptric power 1026 on which the image to be displayed will be mapped.
  • a trial vector 1404 is first generated from the pixel’s position to the pupil center position 1022 of the user’s pupil 1405.
  • pupil center position 1022 may be acquired via eye/pupil tracker 110.
  • a corresponding pupil plane 1406, which may be a flat 2D surface or plane in 3D space centered on pupil center position 1022, may be defined here as well.
  • trial vector 1404 by construction, necessarily has to go through a corresponding optical unit of LFSL 106.
  • step 1106 a new Ray vector 1412 will be similarly generated from a center location/position 1410 of the corresponding optical unit comprising intersection point 1408 of LFSL 106 and pointing to pixel 1402.
  • step 1106 is detailed in the sub-steps 1206 to 1212 shown in Figure 12.
  • sub-step 1206 the location of intersection point 1408 of vector 1404 with the LFSL 106 is calculated as illustrated in Figure 14A.
  • sub-step 1208 the coordinates of the center location 1410 of the optical element or unit of LFSL 106 closest to intersection point 1408 are computed.
  • One way to efficiently compute this location is provided in related U.S. Patent 10,394, 322, the contents of which are incorporated herein by reference.
  • a normalized unit ray vector is generated from normalizing a ray vector 1412 originating from center position 1410 of LSFL 106 and extending to pixel 1402.
  • This unit ray vector thus approximates the direction of the light field emanating from pixel 1402 through the center 1410 of this particular LFSL element, for instance, when considering a parallax barrier aperture or lenslet array (i.e. where the path of light travelling through the center of a given lenslet is not deviated by this lenslet). Further computation may be required when addressing more complex light shaping elements, as will be appreciated by the skilled artisan.
  • step 1212 ray vector 1412 is projected backwards (dotted line 1414 on Figure 14B) to intersect with pupil plane 1406 at location 1416.
  • step 1108 verifies that intersection point 1416 with pupil plane 1406 of projected ray vector 1414 is still located within user pupil entrance 1405 (i.e. that the user can still “see” it).
  • the distance between the pupil center 1022 and intersection point 1416 within pupil plane 1406 may be calculated to determine if the deviation is acceptable, for example by using pre- determined pupil size 1424 and verifying how far the projected ray vector intersection 1416 is from pupil center 1022 within pupil plane 1406.
  • step 1110 method 1100 flags pixel 1402 as unnecessary and to simply be turned off or to render a black color.
  • step 1108 may be modified so that instead of having a binary choice between the ray vector hitting the pupil or not, one or more smooth interpolation function (i.e. linear interpolation, Hermite interpolation or similar) may be used to quantify how far or how close intersection point 1416 is to pupil center 1022 within pupil plane 1406 and outputs a corresponding continuous value between 1 or 0.
  • the assigned value is equal to 1 substantially close to pupil center 1022 and gradually change to 0 as intersection point 1416 substantially approaches the pupil edges or beyond.
  • the branch containing step 1110 may be ignored completely and step 1108 goes directly to step 1112.
  • step 1114 the pixel color value computed therein for pixel 1402 will be modified to be somewhere between the full color value identified therein or black, depending on the value of the interpolation function used at step 1108 (1 or 0).
  • pixels found to illuminate a designated area around the pupil may still be rendered, for example, to produce a buffer zone to accommodate small movements in pupil location, for example, or again, to address potential inaccuracies, misalignments or to create a better user experience.
  • a corresponding image portion of input image 1020 located on the adjusted image plane and its corresponding color value are identified.
  • two different but equivalent adjusted image planes may be used: a virtual image plane 1502 as shown schematically in Figure 15 (i.e. positioned behind pixel display 108), or the retinal plane 1702 as shown in Figures 17A to 17D (i.e behind user pupil 1405).
  • a virtual image plane 1502 as shown schematically in Figure 15 (i.e. positioned behind pixel display 108)
  • the retinal plane 1702 as shown in Figures 17A to 17D (i.e behind user pupil 1405).
  • each variation of steps 1002 and 1112 are listed in the flow diagrams of Figures 13 and 16, respectively.
  • step 1102 is illustrated in Figure 13, in accordance with one embodiment.
  • virtual image planes are selected for ray -tracing in sub-step 1301
  • ray-tracing is done using a virtual image plane 1502 as illustrated in Figure 15.
  • the location or distance of virtual image plane 1502 from pupil plane 1406 may be computed as a function of spherical dioptric power 1026 (i.e. using the thin lens formula or other) and/or minimum reading distance 1028 (and/or related parameters).
  • input image 1020 is mapped onto virtual image plane 1502 so that its size of also scaled so to ensure that the perceived light field image correctly fills pixel display 108 when viewed by the distant user.
  • FIG. 15 An example is shown in Figure 15 wherein virtual image plane 1502 is shown, as an example only, being located at a distance 1028 (in the z direction or depth) from pupil plane 1406, and the size of image 1020 is increased to avoid having the image as perceived by the user appear smaller than the display’s size.
  • sub-step 1601 leads to sub-step 1602.
  • ray vector 1412 is projected towards virtual image plane 1502 (shown as vector 1504 in Figure 15) to find the position of the intersection point 1506.
  • the portion of image 1020 (and its associated colour channel) corresponding to intersection point 1506 on virtual image plane 1502 is identified.
  • a retinal plane herein defined as a 2D plane or surface substantially located at the location of the user’s retina, as the adjusted image plane instead of virtual plane 1502.
  • the adjusted image portion associated with a given pixel/subpixel is computed (mapped) on retinal plane 1702 instead of virtual image plane 1502 considered in the above example, again in order to provide the user with a designated image perception adjustment.
  • a retinal plane may be defined in various ways.
  • the retinal plane 1702 is defined as a 2D plane located at a distance inside the eye equal to eye depth 1034 from the location of pupil center location 1022. It may also be taken to be parallel to pupil plane 1406, as illustrated in Figure 17A to 17D, although it is not required to be so. It is meant to be an approximate location corresponding to the user’s real retina.
  • sub-step 1301 leads to sub-step 1308, where a projected image center position on retinal plane 1702 is calculated.
  • a vector 1704 is drawn originating from the center 1706 of pixel display 108 and passing through pupil center 1022.
  • Vector 1704 is further projected beyond pupil plane 1405 onto retinal plane 1702, and the associated intersection point 1708 gives the location of the corresponding image center on retinal plane 1702.
  • image center 1708 is known, in sub-step 1310 one can scale image 1020 to the x/y retina image size 1710, as illustrated schematically in Figure 17D.
  • the required scaling may be computed by calculating the magnification of an individual pixel on retinal plane 1702, for example, which may be approximately equal to the x or y dimension of an individual pixel multiplied by the eye depth 1034 and divided by the absolute value of the distance to the eye (i.e. thus giving the magnification of the image portion created a pixel once focused by the eye lens on retinal plane 1702).
  • An exemplary scaled inverted image 1712 on retinal plane 1702 is shown in Figure 17D.
  • the input image 1020 may also normalized by the image x/y dimensions to produce a corresponding normalized input image 1714 having a width and height between -0.5 to 0.5 units, which may be compared to inverted scaled image 1712 which may also be similarly normalized.
  • sub-step 1312 is done independently to determine a location of a focal plane as produced by the user’s eye for a given input value of spherical dioptric power 1026 (or minimum reading distance 1028).
  • eye focal plane 1716 shown in Figure 17A and 17B is defined as the location where any light ray originating from optical unit center location 1410 would be focused by the user’s eye.
  • focal plane 1716 would be located at the same location as retinal plane 1702, but in the example shown in Figure 17A and 17B, as an example only, focal plane 1716 is located behind retinal plane 1702, which would be expected for a user with some form of farsightedness.
  • the position of focal plane 1716 may be derived from the user’s minimum reading distance 1028 or spherical dioptric power 1026, for example, by deriving therefrom the corresponding focal length of the user’s eye.
  • Other manually input or computationally or dynamically adjustable means may also or alternatively be considered to quantify this parameter.
  • step 1112 in the case of ray-tracing on retinal plane 1702 has sub-step 1601 leading to sub-step 1608, illustrated schematically in Figure 17A, where a vector 1718 is drawn from optical unit center 1410 to pupil center 1022. Then, in sub-step 1610, vector 1718 is projected further behind pupil plane 1406 onto eye focal plane 1716 where intersection point 1720 is identified.
  • any light ray originating from optical unit center 1410, no matter its orientation, will also be focused onto intersection point 1720, to a first approximation.
  • the location 1722 on retinal plane 1702 onto which light entering the pupil at intersection point 1416 will converge may be approximated, at sub-step 1612, by drawing a straight line between intersection point 1416 where projected ray vector 1414 hits pupil plane 1406 and focal point 1720 on focal plane 1716, as illustrated in Figure 17B.
  • the intersection of this line with retinal plane 1702 (retina image point 1722) is thus the location on the user’s retina corresponding to the image portion that will be reproduced by corresponding pixel 1402 as perceived by the user. Therefore, at sub-step 1614, by comparing the relative position of retinal point 1722 with the overall position of the projected image on the retinal plane 1702, the relevant adjusted image portion associated with pixel 1402 may be computed.
  • the image portion position 1724 relative to retina image center position 1726 in the scaled coordinates corresponds to the inverse (because the image on the retina is inverted) scaled coordinates of retina image point 1722 with respect to retina image center 1708, as shown in Figure 17D.
  • the associated color with image portion position 1724 may be therefrom extracted and associated with pixel 1402.
  • step 1114 pixel 1409 is flagged as having the color value associated with the portion of image corresponding to intersection point 1506 in the case of ray -tracing on virtual image plane 1502 (as shown in Figure 15) or in the case of ray -tracing on retinal plane 1702, to the image portion corresponding to intersection 1725 as shown in Figure 17D.
  • step 1116 a check is made to see if every pixel in pixel display 108 has been ray -traced. If not then method 1100 chooses another pixel 1402 and goes back to step 1104; if so, then the output color of all pixels has been determined and these are finally rendered in step 1118 by pixel display 108 to be viewed by the user, therefore presenting a light field corrected image. In the case of a single static image, the method may stop here. In yet other embodiments, pixels found to illuminate a designated area around the pupil may still be rendered, for example, to produce a buffer zone to accommodate small movements in pupil location, for example, or again, to address potential inaccuracies or misalignments.
  • mapping the input image to a virtual image plane set at a designated minimum (or maximum) comfortable viewing distance can provide one solution
  • the alternate solution may allow accommodation of different or possibly more extreme visual aberrations. For example, where a virtual image is ideally pushed to infinity (or effectively so), computation of an infinite distance becomes problematic.
  • the illustrative process steps of Figures 16 A and 16B can accommodate the formation of a virtual image effectively set at infinity without invoking such computational challenges.
  • first order aberrations are illustratively described with reference to Figure 11, higher order or other optical anomalies may be considered within the present context, whereby a desired retinal image is mapped out and traced while accounting for the user’s optical aberration(s) so to compute adjusted pixel data to be rendered in producing that image.
  • each core is dedicated to a small neighborhood of pixel values within an image, e.g., to perform processing that applies a visual effect, such as shading, fog, affine transformation, etc.
  • GPUs are usually also optimized to accelerate exchange of image data between such processing cores and associated memory, such as RGB frame buffers.
  • smartphones are increasingly being equipped with powerful GPUs to speed the rendering of complex screen displays, e.g., for gaming, video, and other image- intensive applications.
  • Several programming frameworks and languages tailored for programming on GPUs include, but are not limited to, CUD A, OpenCL, OpenGL Shader Language (GLSL), High-Level Shader Language (HLSL) or similar.
  • GLSL OpenGL Shader Language
  • HLSL High-Level Shader Language
  • texture memory is cached on chip and in some situations is operable to provide higher effective bandwidth by reducing memory requests to off-chip DRAM.
  • texture caches are designed for graphics applications where memory access patterns exhibit a great deal of spatial locality, which is the case of the steps 1104 to 1116 of Figure 11.
  • image 1020 may be stored inside the texture memory of the GPU, which then greatly improves the retrieval speed during step 1112 (including either one of the ray- tracing variants presented in Figures 13 and 16) where the color channel associated with the portion of input image 1020 is determined.
  • method 1100 presented above was discussed and illustrated as having each plane (i.e. virtual image plane 1502, pixel display 108, LSFL 106, pupil plane 1406, retinal plane 1702 or eye lens focal plane 1716) as being parallel with each other, this was only done as an example for clarity and to better describe the methodology associated therewith. Indeed, method 1100 as discussed may equally be applied to account for changes in the relative orientation between any one of those planes.
  • ray -tracing with non-parallel planes will now be discussed.
  • cases may be considered wherein the user is viewing the light field display at an angle.
  • the ray-tracing method can therefore account for a change in orientation of the pupil plane 1406 with respect to the pixel display 108 and optical layer 106.
  • other planes such as virtual image plane 1502, and retinal plane 1702 and focal plane 1716 may be taken to be parallel to pupil plane 1406.
  • the relative difference in orientation between the two sets of planes is illustrated by using vector 1802 which is the normal vector to the plane of corresponding optical layer 106, and vector 1804 which is the normal vector to pupil plane 1406.
  • vector 1802 which is the normal vector to the plane of corresponding optical layer 106
  • vector 1804 which is the normal vector to pupil plane 1406.
  • the relative orientation between the two normal vectors is illustrated in Figure 19, using polar and azimuthal angles.
  • the general orientation of pupil plane 1406 may be parametrized, for example, by using the 3D location of pupil center 1022 and a corresponding normal vector 1804.
  • Normal vector 1804 may be taken to be, in some embodiments, equal to the gaze direction as measured by a gaze tracking system or similar, as will be discussed below.
  • the relative position and orientation of pupil plane 1406 may be determined and parametrized accordingly. Planes that are parallel share the same normal vector. From there, the method 1100 and its variants described above may be applied by finding the intersection point between an arbitrary vector and an arbitrarily oriented plane, as is done for example at steps 1206, 1212, 1602, 1610, 1612 for example.
  • the position of virtual image plane 1502 may be computed using spherical dioptric power 1026 (and/or minimum reading distance 1028 and/or related parameters) but from the position of pupil plane 1406 and along the direction vector 1804.
  • the eye tracking methods and systems described above may be used or modified to further provide a measure of the eye’s gaze direction (e.g. gaze tracking).
  • gaze tracking e.g. gaze tracking
  • pupil plane 1406 may be re-parametrized using an updated 3D location of pupil center 1022 and an updated normal vector 1804 at each eye tracking cycle.
  • a hybrid gaze tracking/pupil tracking system or method may be used wherein gaze direction (e.g.
  • normal vector 1804 is provided at a different interval than pupil center location 1022.
  • pupil center location 1022 For example, in some embodiments, for one or more cycles, only the 3D pupil center location 1022 may be measured and an old gaze direction vector may be re-used or manually updated.
  • an eye model or similar may be constructed to map a change in measured pupil center location 1022 to a change in the gaze direction vector without relying on the full capabilities of the gaze tracking system or method. Such a map may be based on one or more previous gaze tracking measurements. In any case, by measuring/determining the 3D pupil center location 1022 and normal vector 1804, the pupil plane may be parametrized accordingly.
  • pixel display 108 and optical layer 106 are shown as being parallel for simplicity, but other embodiments may envision optical layer 106 to be non-parallel to display 108 as well. This doesn’t change the general scope of the present discussion, as long as the relative angle between them is known. For example, such an angle may be pre-determined during manufacturing or measured in real-time using one or more sensors (for example in the case where optical layer 106 may be mobile). Similarly, other planes like for example retinal plane 1702 may also be made to be non-parallel to the pupil plane, depending on the user’s eye geometry.
  • step 2002 shown in Figure 20A is meant to replace step 1102 in method 1100, while step 2012 of Figure 20 B replaces step 1112. This is because the previously above- described steps 1102 and 1112 were directed to correcting a single image by directly or indirectly modifying the location of the virtual image plane and/or eye focal plane.
  • steps 2002 and 2012 are directed to a light field display which is generally operable to display multiple image planes at different locations/depths/aberrations simultaneously.
  • the method continues to sub-step 2102 (illustrated in Figures 21 A) if ray-tracing is done using the virtual image plane or if ray -tracing is done using the retinal plane then sub-step 2300 is used (illustrated in Figures 23 A).
  • sub-step 2104 in the case of ray -tracing to virtual image plane (illustrated in Figure 21B) or to sub-step 2301 (illustrated in Figure 23B if ray-tracing is done using the retinal plane).
  • the methods as herein described may be implemented to generate varying depth perceptions within a same eye, that is, allowing for the monoscopic viewing of an input to exhibit multiple distinct image perception adjustments (i.e. multiple juxtaposed and/or overlapping depths, enhancements or like optical adjustments, compensations, etc.).
  • distinct image planes may be juxtaposed such that different sides or quadrants of an image, for example, may be perceived at different depths.
  • a different effective vision correction parameter e.g. diopter
  • depth may be applied, to each portion or quadrant.
  • steps 2102 and 2104 of figures 21 A and 21B are directed towards ray -tracing on one or more virtual image plane only, while steps 2300 and 2301 of Figures 23 A and 23 B are directed towards ray -tracing on the retinal plane.
  • input image 1020 of input variables 1004 may also include, in addition to pixel data, variable dioptric powers or perceptive “depth” information or parameters.
  • any image or image portion may have a respective depth indicator.
  • a set of multiple virtual image planes may be defined, at sub-step 2108, which includes deriving their respective (virtual) location, similarly to sub-step 1302.
  • any image or image portion on each of these virtual image planes may be optionally scaled to fit the display, similarly as described for sub-step 1304 for a single image plane.
  • FIG. 15 In the previous example shown in Figure 15, a single virtual image plane 1502, showing an exemplary input image 1020 comprising two circles, was used.
  • Figures 22 A to 22D show an example wherein each circle is located on its own virtual image plane (e.g. original virtual plane 1502 with new virtual image plane 2202).
  • the skilled technician will understand that two planes are shown here only as an example and that the method steps described herein apply equally well to any number of virtual planes. The only effect of having more planes is a larger computational load.
  • step 2104 an iteration is done over the set of virtual image planes to compute which image portion from which virtual image plane is seen by the user.
  • a virtual image plane is selected, starting from the plane located closest to the user.
  • step 1602 proceeds as described previously for that selected virtual plane.
  • the corresponding color channel of the intersection point identified at step 1602 is sampled.
  • a check is made to see if the color channel is transparent. If this is not the case, then the sampled color channel is sent to step 1114 of Figure 11, which was already described and where the color channel is rendered by the pixel/subpixel.
  • FIGS 22A and 22B An example of this is illustrated in Figures 22A and 22B, wherein a user is located so that a ray vector 2204 computed passing through optical element center location 1410 and pixel/subpixel 1402 intersects virtual image plane 1502 at location 1506. Since in this example this location is non-transparent, this is the color channel that will be assigned to the pixel/subpixel. However, as this example shows, this masks or hides parts of the image located on virtual image plane 2202. Thus, an example of the image perceived by the user is shown in Figure 22B.
  • sub-step 2114 if the color channel is transparent, then another check is made at sub-step 2116 to see if all virtual image planes have been iterated upon. If this is the case, then that means that no image or image portion is seen by the user and at sub-step 2118, for example, the color channel is set to black (or any other background colour), before proceeding to step 1114 of Figure 11. If however at least one more virtual image plane is present, then the method goes back to step 2110 and selects that next virtual image plane and repeats sub-steps 1602, 2112 and 2114.
  • FIG 22C An example of this is illustrated in Figure 22C, wherein a user is located so that a distinct ray vector 2204 computed passing through optical element center 2206 of LFSL 106 and pixel/subpixel 2208 of pixel display 108 first intersects at location 2210 of virtual image plane 1502. Since, in this example, this location is defined to be transparent (i.e. not on the circle), the method checks for additional virtual image planes (here plane 2202) and extends vector 2204 so as to compute intersection point 2212, which is now non-transparent (i.e. on the circle), and thus the corresponding color channel is selected.
  • FIG 22D An example of the image perceived by the user is shown in Figure 22D.
  • steps 2300 and 2301 of Figure 23A and 23B substantially mirrors steps 2102 and 2104, respectively, described in Figures 21A and 21B, but are herein applied to be used with two or more eye focal planes (e.g. for ray -tracing the image on retinal image plane 1702).
  • the method iterates, after sub-step 1608, over all designated image planes, each corresponding to a different eye focal plane, starting from the plane corresponding to an image located closest to the user.
  • a new eye focal plane is selected at sub-step 2306, which is used for sub-steps 1610 to 1614 already described above.
  • the corresponding image portion is determined at sub-step 1614, at sub-step 2308, the corresponding pixel/subpixel color channel is sampled. Then at sub-step 2310, if the color channel is non-transparent, then the method continues to step 1114 of Figure 11, wherein the pixel/subpixel is assigned that color channel. However, if the image portion is transparent, then the method iterates to the eye focal plane corresponding to the next designated image plane. Before this is done, the method checks at sub-step 2312 if all the eye focal planes have been iterated upon. If this is the case, then no image portion will be selected and at sub-step 2314 the color channel is set to black, for example, before exiting to step 1114. If other eye focal planes are still available, then the method goes back to sub- step 2306 to select the next eye focal plane and the method iterates once more.
  • steps 2102, 2104 or 2300 and 2301 for multiple designated image planes of Figures 21A-B (on virtual planes) or Figures 23 A- B (retinal plane) may be used to implement a phoropter/refractor device to do subjective visual acuity evaluations.
  • a phoropter/refractor device may be used to implement a phoropter/refractor device to do subjective visual acuity evaluations.
  • different optotypes e.g. letters, symbols, etc.
  • a refractive optical component e.g. change in focus/optical power.
  • two images of the same optotype e.g.
  • image 2402 is located on designated image plane 2404 while image 2406 is located on designated image plane 2408, which is located further away.
  • the size of the image may be increased with increased depth so that all images displayed are perceived to be of a similar relative size by the user.
  • figure 24B we see an example of the perception of both images as perceived by a user with reduced visual acuity (e.g. myopia), for example, wherein the image closest to the user is seen to be clearer.
  • a user could be presented with multiple images (e.g. 2 side-by-side, 4, 6 or 9 in a square array, etc.) and indicate which image is clearer and/or and most comfortable to view. An eye prescription may then be derived from this information.
  • the systems and methods discussed herein may also be adapted to correct or compensate for the presence of HO As.
  • This is generally done by digitally simulating the presence of a “virtual” optical element specifically tailored or constructed so as to reproduce the effect of said HO As.
  • a “virtual” optical element will be referred to herein as a phase element, since its effect on an incoming wave front is to introduce a phase shift or phase profile corresponding to one or more known HO As.
  • phase element By considering the effects of such a phase element on each incoming ray generated by a light field display, it is possible to generate an image that compensates for the user’s HO As and thus allows the user to clearly perceive the image.
  • the focus of the methods described below is one treating for HO As
  • the methods using the phase element may generally be applied, without limitation, to simulate other kinds of optical aberrations, such as astigmatism, as will be made clear below.
  • phase element 2500 which is tailored or constructed so as to generate an aberrated output wave front 2504. Since a wave front is defined as asurface of common phase, a corresponding set of light rays may be defined so as to be perpendicular or normal to the wave front surface (incoming rays 2506 and refracted rays 2508).
  • the difference between aberrated output wave front 2504 and input wave front 2502 is in the phase shift caused by one or more HO As (or aberrations in general) of phase element 2500.
  • phase element 2500 so as to reproduce the required phase shift, it is possible to compute therefrom the change in orientation of input rays 2506 to output rays 2508 and construct a light field image using a light field display that compensates for these HO As (or aberrations in general).
  • phase element 2500 is herein illustrated as being parallel to the ( x , y) axis as an example only. More general relative orientations between phase element 2500 and for example light field display 104 or pupil plane 1406 (not shown here) may be assumed, without limitation, as will be noted further below.
  • phase element 2500 may be used to model or digitally replicate HO As (or aberrations in general) in the user’s eye, in which case phase element 2500 may be virtually positioned at the user’s pupil, as illustrated in Figure 26 A.
  • it may be desirable to model HO As (or wavefront modifications) of a real physical optical element located in front of the eye, and thus phase element 2500 may be positioned somewhere in-between the eye and the light field display, as shown in Figure 26B.
  • multiple phase elements 2500 may be deployed simultaneously.
  • Phase element 2500 may be defined or constructed in different ways and may have different geometries or optical characteristics, so long as it correctly models or reproduces the corresponding aberrations of interest. Some non-limiting examples are given below.
  • phase element 2500 may comprise a first incident surface 2700 (facing the light field display), a second surface 2700 (facing the user).
  • first incident surface 2700 may be defined to be flat with a normal vector orientated in the z direction, and only the second surface 2702 having a variable shape profile.
  • Other embodiments may include both surfaces having a variable shape or profile, as illustrated in Figure 27C.
  • phase element 2500 is not limited to having a rectangular shape, as was illustrated in Figures 26A-C and 27A only as an example. Different considerations may be taken into account to determine the shape, size or extension of phase element 2500 in the (x, y) and z dimensions. In some embodiments, for example when Zernike polynomials are used to generate the shape of phase element 2500, a disk shape, as in Figure 27D, may be used, so as to better align with the pupil shape and the azimuthal and radial dependent forms of the Zernike polynomials. Generally, the size in the (x, y) plane will be chosen so that all light rays projected from the light field display may be properly refracted.
  • the x, y coordinates may be chosen as being equal to a factor of the pupil radius, so as to ensure that all rays encountering the pupil are considered.
  • different in-plane shapes herein shown as a disk-shape or circular profile
  • phase element 2500 may comprise multiple layers (not shown), each layer having its own refractive index, thus comprising a multiplicity of internal surfaces in addition to the external surfaces 2700 and 2702 (not shown).
  • phase element 2500 considered will consist of a phase element having a circular profile (as in the diagram of Figure 27D), but having a flat or plane-like first surface 2700 and a second surface 2702 having a variable shape, depth, height or profile defined via a height or thickness function h(x,y ), as illustrated schematically in Figure 28.
  • function h(x,y ) may thus give the height or depth z-position of second surface 2702 as measured perpendicularly from the z-position of first surface 2700 for all ( x , y) values.
  • phase element 2500 is thus constructed by computing the height or thickness function h(x, y) (in conjunction with a refractive index n) that reproduces the required HO As (or aberrations in general).
  • the required aberrational phase shift may be defined using Zernike Polynomials, for example.
  • the required phase shift may be derived from measurements or the like, for example a lens profile measurement or wave front measurement.
  • the embodiments discussed below will use Zernike polynomials, as an example only, since they are commonly used as a complete set of functions to represent the effect of any optical element or aberration on an incoming wave front.
  • other decomposition functions or polynomials may be used, for example and without limitation, Seidel series, Fourier series, Taylor polynomials, elliptical polynomials, etc.
  • small beams may be assumed when sampling the phase element 2500, so that the divergence or convergence due to the presence of the phase element may be minimal.
  • the various embodiments described below will use such an approximation, also as an example only.
  • method 2900 as illustrated in Figure 29 is an extension of method 1100 discussed above, but now includes the effects of incorporating one or more phase elements 2500 to treat HOAs (or aberrations in general). While some steps are similar as those described above, other steps have been modified or added as required.
  • the image or optotype to be displayed is prepared. This is illustrated in Figure 30, where, at sub-step 3002, one or more virtual phase elements 2500 are constructed or defined. This includes, in part, defining the required geometry and optical properties of each phase element 2500 so as to reproduce the required aberrational phase shift, as was explained above. Notably, in some embodiments, multiple phase elements 2500 may be used simultaneously, as will be discussed below.
  • sub-step 3002 An example of sub-step 3002 is shown in Figure 31 A. There, an iteration over all the phase element(s) 2500 to be constructed or defined is made starting at sub-step 3101. For each phase element 2500, its geometry and refraction index are computed at sub-step 3102 and its orientation and location at sub-step 3104. At sub-step 3105 the method proceeds back to sub-step 3101 if more phase elements are to be used.
  • a given phase element 2500 is defined or constructed in sub-step 3102 to reproduce a phase shift as defined by a given Zernike polynomial which may be characterized by a corresponding set of Zernike coefficients 1036.
  • it is designed so as to comprise a first input surface 2700 (facing the light field display) that is flat and parallel to the ( x , y) plane (as an example only) and second output surface 2702 (facing the user) which has a profile or shape that varies as a function of planar position ( x , y).
  • a refractive index 1038 (n) of phase element 2500 is also chosen accordingly.
  • refractive index 1038 is not meant to reproduce exactly the refractive index of a real optical element (external lens or user’s eye), but it is chosen so that, in combination with the height function h(x,y ), the phase element 2500 properly or correctly reproduces the chosen HOAs (or aberration in general) evaluated by comparison to diffraction patterns of wavefronts (for example such as those illustrated in Figures 32A and 32B).
  • height function h(x,y ) is known analytically, corresponding analytical expressions for the normal vector functions of the second surface 2702 may also be used.
  • height function h(x,y ) and refractive index/indices may be derived from experimental data or similar, and thus they can be used directly, and it may be required to use numerical derivatives or similar methods to compute the normal vectors.
  • the data points can be fitted to smooth analytical functions to reduce the numerical errors in calculating the derivatives.
  • the pre-computed or measured height or thickness function h(x,y ) of phase element 2500 and the associated pre-computed normal vector coordinates may be stored digitally in an array structure or similar.
  • these values may be stored via a texture object or similar, for ease and speed of access.
  • different “resolutions” of the texture object may be used, so as to “coarse-grain” the geometry as required by considerations of speed of computation, as will be further discussed below.
  • the HO As are decomposed or described mathematically using Zernike polynomials . These polynomials are used to represent or define deviations or shifts from a desired wave-front. Since a wave-front is a plane of uniform phase, the Zernike phase shift describing the effect of one or more optical aberrations may be written as, for example:
  • the spatial dependent height or thickness h(x,y) of phase element 2500 may be computed using a corresponding phase shift function, f(c, y), which represents the effect of HO As (or aberrations in general) on an incoming wave front, and at least one corresponding refractive index 1038 (n) of phase element 2500.
  • the phase shift may be constructed on a plane parallel to the lens principal plane using a multiplicity of parallel rays passing through the interior of phase element 2500, again as was illustrated in Figure 25.
  • phase element 2500 and the remnant distance to reach the phase-construction plane may be considered.
  • the geometry and refraction index of one phase element 2500 is generated from the input set of Zernike coefficients 1036.
  • a thin element assumption or approximation may be used, so that the phase-change or phase- shift as a function of (x, y) coordinates generated by phase element 2500 may be written as: which, excluding the constant phase term, gives a height or thickness as a function of the (x,y) coordinates of: where no is the medium refractive index and n is the refractive index 1038.
  • phase element 2500 may be derived in different ways, as required.
  • the continuity of the tangential wave-vector component may be used to derive ray refraction equations.
  • the position (x T , y r )of the transmitted ray through a surface is the same as the incident ray (x / ,y / ), thus:
  • a normal of the surface vector and a corresponding incident ray wave- vector define the plane of incidence. This plane can be defined by the normal that is calculated by the cross product:
  • the angle of incidence ( ⁇ I ) between the surface normal and the ray wave- vector is given by:
  • the incident wave vector can be decomposed in terms of the surface normal vector and a surface tangential vector :
  • the transmitted ray directi on- vector may be calculated by considering that the continuity of the tangential component of the wave vector and the change in its magnitude. Again, representing the transmitted component as normal and tangential components, in the plane of incidence:
  • corresponding analytical expressions for the normal unit vectors on the surface at every location h(x,y ) may be derived using the gradient of the surface. Assuming the height or thickness is in the z direction only, for a function of the form: the normal unit vectors to the surface are given by: where m is the medium refractive index and n is the phase element refractive index 1038. In air, this gives:
  • a variety of optimizations may be employed. As mentioned above, analytical forms of the derivatives may be used. In addition, a high value of refractive index 1038 may also be used to minimize the thickness of phase element 2500 (although precautions must be taken so as to avoid the total internal reflection regime).
  • a constant height or thickness value may be subtracted before computing ray propagation inside the element. For example: where min(h(x,y)) is the minimum value of function h(x,y).
  • a thin lens assumption may be used for phase element 2500.
  • the second surface 2702 herein modelled as an ideal thin lensing surface may (with no approximation) may be given by: where / is the focal length of phase element 2500; which, for the paraxial limit gives:
  • transfer matrix model may be used.
  • the spatial coordinates do not change, on the other hand the wave-vector angle is given by:
  • any phase shift ⁇ (x, y) may be represented via a Zernike polynomial in the form of: and where the normal vectors to the non-flat surface of the corresponding phase element, in air, are given by: [00268]
  • the corresponding height or thickness function h(x, y) and a corresponding set of normal vector functions for the second surface may be computed.
  • the refractive index and shape of phase element 2500 may be obtained by trial and error to match, for example, a refracted beam produced by phase element 2500 with a diffraction profde or by profiling a real optical element.
  • r is the polar radial coordinates normalized to the pupil radius ( R ) and Q is the polar angular coordinate and z is the corresponding contribution to the height or thickness h(x,y ).
  • Zernike coefficients may be derived in different ways, as is well known in the art.
  • an astigmatism prescription may be converted to a Zernike phase shift function and vice-versa.
  • the corresponding coefficients of concern here are: S: the spherical dioptric power 1026, C: cylindrical dioptric power 1030, the cylinder axis angle 1032, and Rp: the pupil radius.
  • S the spherical dioptric power 1026
  • C cylindrical dioptric power 1030
  • Rp the pupil radius.
  • the relation to the relevant Zernike coefficients 1036 may be given through the following relations:
  • phase element 2500 is “virtually” positioned at the correct location and with the correct orientation.
  • first surface 2700 of phase element 2500 is always considered to be parallel to the ( x , y) plane, but more general orientations may be considered. Computations with non-parallel surfaces may take into account the required rotational and translational transformations as necessary.
  • phase element may be located at a given distance from the user’s eye (so to model a real external lens) or it may be located (via the position of the first surface 2700) at pupil plane 1406 (to model an eye aberration).
  • sub-step 3002 continues as discussed above in the context of Figure 13 (i.e. sub-steps 1301 to 1312), again depending on whether ray- tracing is done using the virtual image plane or the retinal plane.
  • step 2908 is where rays are propagated and interacted with each phase element 2500.
  • more than one phase element 2500 may be used simultaneously, as illustrated schematically in Figure 44.
  • These phase elements 2500 may or may not have the same optical properties, as required.
  • this exemplary embodiment of step 2908 further includes the possibility of having a phase element 2500 at the pupil plane itself, so as to model an aberrated eye, or direct compensation therefor.
  • ray 1414 is propagated in a straight line towards the eye until it either encounters an element 2500 in its path (via first surface 2700), or until it reaches the pupil plane 1406.
  • a check is made to see if the ray as reached the pupil plane. If not, then it has encountered a first surface 2700 of a phase element 2500 in its path.
  • the refracted ray obtained from this phase element 2500 is computed.
  • phase element 2500 is shown to be located somewhere between the eye and the light field display.
  • first surface 2700 is shown being located at a distance 3450 from pupil plane 1406.
  • distance 3450 would be zero and first surface 2700 would be at pupil plane 1406.
  • ray 1414 is shown encountering a first surface 2700 of a phase element 2500 at input location 3404, which produces a corresponding refracted ray 3402 exiting from second surface 2702 at output location 3406.
  • both the origin and orientation of refracted ray 3402 exiting phase element 2500 is computed. It is this ray that is propagated.
  • incoming ray 1414 will intersect the first surface 2700 at input location 3404 (herein corresponding to x, y coordinates (x 0 , y 0 ), be refracted as ray 3602, which will travel within phase element 2500 until it reaches second surface 2702 at output location 3406 (herein corresponding to x,y coordinates (x 1 , y 1 ) , where it will once again be refracted.
  • the location in z of output location 3406 is given by the height or thickness profile function at this point, i.e. h(x 1 , y 1 ).
  • Refracted ray 3402 is thus the refracted ray or ray vector exiting phase element 2500 at output point 3406.
  • the normal vector n to first surface 2700 is by definition parallel to the z-axis, while the normal vectors of the second surface 2702 are defined as a function of x,y coordinates: , as was discussed above.
  • the normal vector at second surface 2702 is given by
  • ray 3602 is projected forward within phase element 2500 using small propagation steps until the height or thickness traversed is equal or larger than the height or thickness at the current iteration, at which point the second refraction event is computed.
  • this requires the use of small steps and thus many iterations may be required.
  • output location 3406 may be approximated (e.g. thin lens approximation) as being the same as input location 3404 (i.e. (x 0 , y 0 ) ⁇
  • input location 3404 i.e. (x 0 , y 0 ) ⁇
  • the corresponding z-coordinate and normal vectors are given by h(x 0 ,y 0 ) and normal vector n(x 0 ,y 0 ).
  • ray 3602 may be propagated inside phase element 2500 a distance equal to the height or thickness at the first intersection position h(x 0 , y 0 ) and then the normal vector at the new coordinates (x 3 , y 3 ) may be used to compute the second refraction event.
  • the values of functions h(x,y ) and n(x,y ) may be pre-computed and stored in an array-like data structure, for example in a texture file. An example is given schematically in Figures 37A to 37C.
  • the exemplary phase element 2500 of Figure 37A may be stored as a pre-computed array of height or thickness values herein represented as digitized phase element 4402 in Figure 37B.
  • each portion (i,j) i.e. array index number
  • h(i,j) and normal vector n(ij ' ) corresponds to a given height value h(i,j) and normal vector n(ij ' ).
  • the resolution of phase element 4402 may be changed as required by computational considerations, thus varying the corresponding size of each portion ( dx, dy ).
  • Figure 37C shows a cross-sectional view of Figure 37B superimposed on the surfaces 2700 and 2702 of the exemplary phase element of Figure 37A.
  • each portion corresponds to a texel (texture pixel) or similar and thus a corresponding (x, y) coordinate (for example input location ( x , y) located within a given portion may be converted to the appropriate index (i ) to access the corresponding height and normal vector).
  • interpolated values for the height and normal vector may be generated as a function of the relative position of input location ( x , y) with respect to the neighboring texel locations. This may include for example linear interpolation but other interpolation methods may also be used.
  • the pre-computed set of values h(i,j ) may be sorted from smallest to largest, and then checked iteratively while propagating ray 3602 until the height or thickness at the newly obtained ( x , y) coordinates is within a given tolerance interval.
  • refracted ray 3402 will be perceived by the user, via projection 3408, as originating from a “virtual” optical element center 3410 (e.g. “virtual” lenslet or microlens center position) and corresponding “virtual” pixel 3412.
  • a “virtual” optical element center 3410 e.g. “virtual” lenslet or microlens center position
  • each set of “virtual” pixel 3412 and associated “virtual” optical element center 3410 computed from each pixel in the pixel display may be computed once and kept or stored in memory for later iterations.
  • sub-step 3510 proceeds just like sub-step 3504 and the new refracted ray 3402 is computed, just as discussed above. If no phase element was present at the pupil plane at sub-step 3508, or when the new refracted ray 3402 is computed at sub-step 3510, step 2908 exits with the YES condition, so that in method 2900 of Figure 29, the method then proceeds to step 2912.
  • the last computed refracted ray 3402 (and its projection 3408 and “virtual” optical element center location 3410) may be used to replace ray 1414 in step 2912, which is illustrated in Figure 38 and comprises the same sub-steps as step 1112 of Figure 16, but with some changes, as will be discussed below.
  • step 2912 proceeds via sub-step 1601 as discussed above where the path changes depending on whether the ray-tracing is done on the virtual image plane or on the retinal plane. If it’s the former, then sub-step 1602 is executed to identify the image portion on virtual image plane 1502, just like as described above in the context of Figure 16, but here it is the intersection point of projection vector 3408 on virtual image plane 1502 (instead of vector 1504) which provides the corresponding image portion 1506 in Figure 15.
  • sub-step 3808 is executed.
  • the real optical element center location 1410 instead of using the real optical element center location 1410 to draw vector 1718 through pupil center 1022, it is instead the “virtual” optical element center location 3410 that is used instead.
  • the ray-tracing steps illustrated in Figures 17A to 17D apply equally here as well, with the exception that point 1410 in Figure 17A is replaced by point 3410.
  • sub-steps 1610 to 1614 proceed as explained above to identify the image portion 1724.
  • steps 1114, 1116 and 1118 proceed just like in method 1100.
  • Method 3900 is to method 2900 what the steps discussed above and illustrated in Figures 20A to 23B were for method 1100: it allows the light field display to render multiple optotypes or images simultaneously at different correction levels.
  • method 3900 as discussed below further includes the possibility of using multiple phase elements, but here wherein one distinct phase element is used for each image or optotype being rendered, and wherein each element has its own optical properties and thus simulates a different set of HO As (or aberrations in general).
  • Each set of HO As (or aberrations in general) may also be defined via its own set of Zernike coefficients 1036.
  • each set of HO As may also be used in conjunction with a corresponding spherical dioptric power 1026, which will be used to define either a corresponding virtual image plane 1502 or an eye focal plane 1716, depending on the ray-tracing path chosen.
  • step 3902 begins with step 3902, which mirrors in part step 2002 of Figure 20A.
  • step 3902 further includes, prior to sub-step 2400, sub-step 4002 where multiple phase elements may be constructed (for example one for each optotype being rendering simultaneously).
  • Sub-step 4002 is illustrated in the process flow diagram of Figure 41, where at sub-step 4102 a corresponding correction for a given set of HO As (or aberrations in general) (for a given image portion or optotype) is selected (and its corresponding set of Zernike coefficients 1036). Then this set of Zernike coefficients is used to generate and place a corresponding phase element 2500 in sub-step 3102 and 3104 as discussed above.
  • sub-step 4104 if other sets of HO As (or aberrations in general) are to be included, the method goes back iteratively to sub-step 4002 as many times as necessary, until all corresponding phase elements have been generated. Going back to Figure 40 A, after sub-step 4002, steps 2004, 2102 and 2300 proceed just as described above for each virtual image plane (sub-step 2102) or eye focal plane (sub-steps 2300).
  • sub-step 3810 is similar to step 2104 of Figure 21B, but includes at sub-step 4210 a loop not only over corresponding spherical dioptric power 1026 values but also over associated (if any) HO As and their corresponding phase element. So, once a combination of virtual image plane and phase element is selected, the method uses these to execute sub-step 3208, as described above. If, as computed within sub-step 3208, the ray (either ray 1414 or refracted ray 3402) does not reach inside the user pupil, then the method goes to sub-step 1110, described above.
  • sub-step 1602 the image portion on the virtual image plane is identified.
  • the color channel of this image portion is identified at sub-step 2112, as before.
  • sub-step 2114 if the channel is transparent, then a check is made if all combinations of virtual image planes and phase elements have been used at sub-step 4216, if not then the method goes back to sub-step 4210. If, at sub-step 4216 all combinations have been used and no non-transparent color channel has been encountered, then the method goes to sub-step 2118, as discussed above, so that the color is set to black (or another background color).
  • sub-step 4006 is executed.
  • Flow process diagram of Figure 43 illustrated one embodiment of sub-step 4006.
  • a loop is executed over all sets of spherical dioptric power 1026 values but also over corresponding associated (if any) HO As and their corresponding phase element at sub-step 4310.
  • sub-step 3208 is executed just as described above, and thus includes refraction by the corresponding phase element 2500 but also a check on whether the ray (either ray 1414 or refracted ray 3402, depending on the location of this particular phase element 2500) hits inside the pupil opening.
  • step 1110 is executed as discussed above. If it does hit within the pupil opening, then steps 3808, 1610, 1612 and 1614 are executed one after the other as discussed above in the context of Figure 38, where the “virtual” optical unit center location 3410 is used instead of the optical unit center location 1410 to draw vector 1718.
  • step 2308 is executed to assign the corresponding colour channel to pixel 1402.
  • sub-step 2310 is executed where, as explained above, the colour channel is checked to see if it has been defined as transparent. If it is not, then the colour value is retained and sub- step 4006 is exited.
  • step 4312 is executed to see if all of the corresponding sets of eye focal planes and phase elements have been iterated upon. If not, then the method goes back to sub-step 4310 with the next eye focal plane and phase element. If no phase element and eye focal plane is left, then sub-step 2825 is executed as described before, so that the corresponding colour channel is set to black (or another background colour), before exiting sub-step 4006.
  • step 1114 colour channel is assigned to pixel 1402.
  • Steps 1116 check if all pixels or sub- pixels have been processed
  • 1118 wherein the image is rendered via pixel display 110 proceed as explained before.
  • a unified light field rendering method incorporating phase elements generally referred to using the numeral 4500.
  • this method is used to project a scene from a light field display using the “virtual” pixel and optical unit center (i.e. like “virtual” pixel 3412 and an associated “virtual” optical unit center 3410 discussed above and with reference to Figure 34).
  • the method is to be implemented without the need of transforming the projected scene to an image plane or projection on retina.
  • the role of the light-field algorithm, here, is to sample the scene/virtual object using the generated rays after considering eye aberrations using the phase element.
  • the retinal spot size and spacing control is to be handled with optics design to control the generated beam characteristics.
  • a virtual object/scene is set at a position regardless of the refractive error (e.g. aberration) of the user’s eye. Then at step 4504, an aberration-free eye is assumed to perceive the reconstructed scene without defects.
  • any refractive error that aberrates the eye and needs to be corrected via light field rendering is lumped into one or more phase elements 2500, as discussed above, each element having the required position and orientation.
  • step 4508 for each pixel 1402 in pixel display 108, rays are propagated through the corresponding optical element center 1410 and refraction events from the one or more phase elements 2500 are computed to derive a final refracted ray (i.e. ray 3402 in Figure 34).
  • each ray 3402 is shifted or translated to the nodal point of the eye lens (e.g. to cross pupil center location 1022 for example), as illustrated schematically in Figure 46.
  • a ray 3402 (with a corresponding virtual optical unit center location 3410 and associated virtual pixel location 3412) being shifted to intersect pupil center location 1022, thus giving ray 4602.
  • another set of virtual pixel location 4604 and virtual optical unit center location 4606 may be found.
  • D LE is the distance between the LFSL 106 and pupil plane 1406
  • D is the distance between the pupil and the retina (i.e.
  • raytracing may be done, using different methods, such as method 1100 for example, by using virtual pixel location 4604 and virtual optical unit center location 4606 in place of the real pixel location and optical unit center location (thus using ray 4602 instead of ray 1414).
  • ray 4602 may, for example, by projected backwards to a scene or object 4608 (i.e. for example like ray 1504 on virtual image plane 1502) to identify an corresponding image portion to be assigned to the corresponding pixel.
  • method 4500 may be applied in a recursive manner or by full tracing of the beams generated by the lenslets-pixels combinations starting from the element closer to the lenslet (Dpoi to DP O3 in Figure 44) and ending by the eye pupil, taking into account the required space transformation.
  • the lenslets and pixel coordinates are updated after each iteration then the refracted phase element is removed for the following iteration.
  • the virtual positions of lenslets and pixels are calculated, and light field raymarching is applied.
  • inverse transformation can be done or the whole system is transformed including the virtual object all the way through.
  • the scene objects/charts are sorted in space in the positions and scales they are desired to be viewed.
  • a phase element is constructed, and virtual positions are calculated for the lenslets and pixels.
  • Ray- tracing is done for each prescription/scene object combination. The pixels of rays that hit the prescription region being calculated are excluded from the following prescription calculation.
  • phase element is constructed to correspond to refraction/phase profile of these elements then the regular procedure is applied as explained in steps 4502 to 4512 above.

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Abstract

Sont décrits ici divers modes de réalisation d'un dispositif de champ lumineux, un procédé de compensation d'aberration optique ou de rendu de simulation et un système de test de la vision utilisant ceux-ci. Dans un mode de réalisation, le procédé comprend les étapes suivantes : pour chaque pixel donné, définir numériquement un élément de phase virtuelle défini pour produire un décalage de phase optique désigné correspondant à l'aberration optique ; projeter numériquement une trace de rayon d'image ajusté à partir dudit pixel donné vers un emplacement de pupille d'utilisateur, compte tenu d'un LFSE correspondant associé à celle-ci le long dudit tracé de rayon d'image ajusté, qui coupe ledit élément de phase virtuelle ; calculer numériquement une trace de rayon réfracté correspondante qui résulte de l'intersection de ladite trace de rayon d'image ajusté avec ledit élément de phase virtuelle ; projeter numériquement ladite trace de rayon réfracté afin que celle-ci coupe un emplacement de plan d'image ajusté sur un plan d'image ajusté désigné, et effectuer un rendu, pour chaque pixel donné, de la valeur d'image ajustée qui lui est associée.
PCT/IB2021/051868 2018-10-22 2021-03-05 Dispositif de champ lumineux, procédé de compensation d'aberration optique ou de rendu de simulation et système de test de la vision utilisant ceux-ci WO2021176416A1 (fr)

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IL295827A IL295827A (en) 2020-03-05 2021-03-05 A light field device, optical distortion compensation, or simulation method, and a vision test system that uses them
EP21764574.6A EP4115231A4 (fr) 2020-03-05 2021-03-05 Dispositif de champ lumineux, procédé de compensation d'aberration optique ou de rendu de simulation et système de test de la vision utilisant ceux-ci
CA3167642A CA3167642A1 (fr) 2020-03-05 2021-03-05 Dispositif de champ lumineux, procede de compensation d'aberration optique ou de rendu de simulation et systeme de test de la vision utilisant ceux-ci
US17/510,297 US11500460B2 (en) 2018-10-22 2021-10-25 Light field device, optical aberration compensation or simulation rendering
US17/652,656 US11500461B2 (en) 2019-11-01 2022-02-25 Light field vision-based testing device, system and method
US17/819,885 US11762463B2 (en) 2018-10-22 2022-08-15 Light field device, optical aberration compensation or simulation rendering method and vision testing system using same
US17/957,464 US11789531B2 (en) 2019-01-28 2022-09-30 Light field vision-based testing device, system and method
US18/343,642 US20230341934A1 (en) 2018-10-22 2023-06-28 Light field device, optical aberration compensation or simulation rendering method and vision testing system using same

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US16/810,143 US10761604B2 (en) 2018-10-22 2020-03-05 Light field vision testing device, adjusted pixel rendering method therefor, and vision testing system and method using same
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US16/854,787 US10860099B2 (en) 2018-10-22 2020-04-21 Light field display, adjusted pixel rendering method therefor, and adjusted vision perception system and method using same addressing astigmatism or similar conditions
US16/854,787 2020-04-21
PCT/IB2020/057887 WO2021038421A1 (fr) 2019-08-26 2020-08-22 Dispositif de test de vision de champ lumineux, procédé de rendu de pixels ajusté pour celui-ci, et système de test de vision et procédé utilisant celui-ci
IBPCT/IB2020/057887 2020-08-22
PCT/US2020/058383 WO2021087375A1 (fr) 2019-11-01 2020-10-30 Dispositif à champ lumineux, procédé de restitution de pixels à perception variable associé, système de perception variable et procédé utilisant celui-ci
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PCT/US2020/058383 Continuation-In-Part WO2021087375A1 (fr) 2018-10-22 2020-10-30 Dispositif à champ lumineux, procédé de restitution de pixels à perception variable associé, système de perception variable et procédé utilisant celui-ci

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